PCR-Activated Sorting (PAS)

ABSTRACT

The methods described herein, referred to as PCR-Activated Sorting (PAS), allow nucleic acids contained in biological systems to be sorted based on their sequence as detected with nucleic acid amplification techniques, e.g., PCR. The nucleic acids can be free floating or contained within living or nonliving structures, including particles, viruses, and cells. The nucleic acids can include, e.g., DNA or RNA. Systems and devices for use in practicing methods of the invention are also provided.

CROSS-REFERENCE

This application claims the benefit of U.S. Provisional Application No.62/018,400, filed Jun. 27, 2014, which application is incorporatedherein by reference in its entirety.

INTRODUCTION

Biological systems often contain large and diverse collections oforganisms. Interrogating the nucleic acids in these systems is avaluable method for studying what genes and species are present andunderstanding the system's overall properties. However, the diversity ofthe nucleic acids and organisms in common biological systems often makesdirect study of the system through sequencing of all nucleic acidspresent challenging or impossible, since the very large numbers ofsequences obtained tend to convolute the analysis process.

By way of example, microbial communities, which play important roles ingeochemistry, exist in staggeringly diverse ecosystems. Understandingthe genetics of the cells that inhabit an ecosystem may be critical tounderstanding how microbes function individually and in the complexnetworks that make up the natural environment. Studying the genetics ofindividual microbes, however, is difficult because most cannot becultured in the laboratory and comprise uncultivable “microbial darkmatter”. To study uncultivable microbes, cultivation-free methods likeshotgun sequencing have been utilized. In this approach, nucleic acidsare purified out of a heterogeneous sample via chemical means, shearedinto short fragments, and sequenced. To assemble the resultingcompilation of short sequences into a larger coherent dataset,computational algorithms are utilized, but this process is oftenhampered by the lack of sequencing depth and the complexity of thediverse set of sequences obtained. As a result, next-generationsequencing of diverse communities commonly yields information about thegenes present in a system but is unable to tell how those genes arebundled into genomes and packaged into individual cells. The inabilityto correlate sequences present within a single microbe prevents theassociation of distinct biosynthetic pathways that interact to formimportant phenotypes that can impact the global ecology of the system.Moreover, in such analyses, the genes of rare microbes are difficult todetect since they tend to be swamped out by the sequences of theoff-target microbes that greatly outnumber them. This makes studyinglow-abundance microbes with interesting phenotypes particularlydifficult.

One strategy for obtaining the genomic sequences of rare microbes in adiverse population is target enrichment. In this approach, fragments ofthe genomes of the target microbes are recovered by hybridization tocapture probes. Sequence complementarity between the probes and targetsallows the molecules to anneal, so that the target fragments can berecovered via probe enrichment. A limitation of probe capture, however,is that recovering whole microbial genomes requires hundreds orthousands of overlapping capture probes, necessitating substantialknowledge of the target sequence, which may not be available. Moreover,even when capture probes can be designed, the fragments captured arelimited to those near the sequences targeted by the probes, biasing whatcan be detected by what is already known; this precludes recovery ofwhole genomes in many instances and, thus, prevents complete geneticcharacterization of the species of interest. This is particularlyproblematic when the horizontal transfer of genetic elements occursbecause, in such unpredictable instances, these sequences are not knownto exist in the species of interest and, thus, it may not possible toconstruct probes with which to capture them. Horizontal gene transfer isan important method by which microbes transfer genetic information andgenerate phenotypic diversity, which is why detecting such events isimportant for increased understanding of microbe evolution.

To overcome the limitations of probe hybridization capture, a superiormethod would be to label the target microbes with a specific reporter;the labeled cells could then be recovered, together with their wholegenome, using ultrahigh-throughput fluorescence-activated cell sorting(FACS). One method for accomplishing this is to chemically fix andpermeabilize microbes and then bind to their nucleic acids probeslabeled with fluorescent dyes; the then fluorescent cells can be sortedwith FACS, a method known as fluorescence in-situ hybridization,fluorescence-activated cell sorting (FISH-FACS). FISH-FACS has enormousbenefits over probe hybridization capture because it allowscultivation-free enrichment of the whole genome of the microbe ofinterest. However, FISH-FACS also has drawbacks that significantly limitits applicability for sequencing microbes. For example, fixation canchemically modify DNA and introduce sequencing bias and errors into thegenomes recovered, yielding poor sequence data. More importantly,achieving bright, specific labeling of the cell type of interestrequires substantial trial-and-error optimization of the fixation andpermeabilization procedure, something that may not be possible whenseeking to recover the genome of a cell that cannot be cultured in thelab. This is particularly challenging when screening natural samplescontaining large numbers of different microbes with distinct cell walland membrane properties. Consequently, while FISH-FACS holds enormousutility for the in-situ identification of nucleic acid sequences inuncultivable microbes, it does have drawbacks which limit its routineuse for sequencing purposes. To enable the robust whole-genomesequencing of rare, uncultivable microbes, a new method for enrichingintact microbial genomes out of a diverse ecosystem is needed.

The present disclosure addresses the above issues and provides relatedadvantages.

SUMMARY

This application incorporates herein by reference the entire disclosureof PCT Application No. PCT/US2013/054517, published as WO/2014/028378.

The methods and systems described herein, referred to as PCR-ActivatedSorting (PAS), allow nucleic acids contained in biological systems to besorted based on their sequence as detected with nucleic acidamplification techniques, e.g., PCR. This sorting allows for theenrichment of target sequences of interest from a sample while largeamounts of off-target “background” DNA are discarded such that when thematerial is sequenced the majority of the reads obtained are from thetarget molecules of interest. The nucleic acids can be free floating orcontained within living or nonliving structures, including particles,viruses, and cells. The nucleic acids can include, e.g., DNA or RNA.Systems and devices for use in practicing methods of the invention arealso provided.

Generally, the disclosed methods include encapsulating an aqueoussample, which may include a heterogeneous population of cells, viruses,and/or nucleic acids, in a plurality of microdroplets, wherein eachmicrodroplet includes an aqueous phase fluid in an immiscible phasecarrier fluid. In some embodiments, the sample may be diluted prior toencapsulation, e.g., so as to encapsulate a controlled number of cells,viruses, and/or nucleic acids in the microdroplets. PCR reagents may beadded to the microdroplets at the time of encapsulation or added to themicrodroplets at a later time using one or more of the methods describedherein, e.g., picoinjection, droplet merger, etc. The microdroplets arethen subjected to PCR amplification conditions, such that if amicrodroplet contains a nucleic acid corresponding to a target ofinterest, e.g., a cell, virus, or nucleic acid of interest, themicrodroplet becomes detectably labeled, e.g., fluorescently labeled asa result of a fluorogenic assay, such as Sybr staining of amplified DNAor TaqMan PCR. To recover the target nucleic acids or entitiescomprising the target nucleic acids, the detectably labeled droplets maybe sorted using microfluidic (e.g., dielectrophoresis, membrane valves,etc.) or non-microfluidic techniques (e.g., FACS).

In some embodiments, a method for sorting samples including nucleicacids, is provided, wherein the method includes encapsulating a sampleincluding nucleic acids in a plurality of microdroplets, eachmicrodroplet including a first aqueous phase fluid in an immisciblephase carrier fluid; introducing polymerase chain reaction (PCR)reagents and a plurality of PCR primers into the microdroplets;incubating the microdroplets under conditions sufficient for PCRamplification to produce PCR amplification products, wherein theplurality of PCR primers include one or more primers that each hybridizeto one or more oligonucleotides; introducing a detection component intothe microdroplets either before or after the incubating; detecting thepresence or absence of the PCR amplification products by detection ofthe detection component, wherein detection of the detection componentindicates the presence of PCR amplification products; and sorting themicrodroplets based on detection of the detection component, wherein thesorting separates microdroplets including the PCR amplificationproducts, when present, from microdroplets which do not include the PCRamplification products. One or more of these steps may be performedunder microfluidic control.

In some embodiments of the above method, after the incubating, andbefore or after the detecting, the microdroplets may be positioned in anaqueous phase carrier fluid, e.g., by flowing the microdroplets througha double emulsion droplet maker, to provide aqueous phase-in-immisciblephase-in aqueous phase microdroplets. The aqueous phase-in-immisciblephase-in aqueous phase microdroplets may then be sorted based ondetection of the detection component, wherein the sorting separatesaqueous phase-in-immiscible phase-in aqueous phase microdropletscomprising the PCR amplification products, when present, from aqueousphase-in-immiscible phase-in aqueous phase microdroplets which do notcomprise the PCR amplification products. One or more steps of the methodmay be performed under microfluidic control.

In some embodiments, referred to herein as PCR-Activated Virus Sorting(PAVS), a sample including viruses is encapsulated in microdroplets andsubjected to PCR conditions, e.g., droplet PCR. In some embodiments, theencapsulated viruses are subjected to one or more virus lysingtechniques, such as proteinase k digestion or thermal lysis. PCR assaysspecific to the viruses of interest can cause microdroplets containingthe viruses of interest to become detectably labeled, e.g.,fluorescently labeled. The viruses are then recovered by sorting themicrodroplets and recovering their contents via microdroplet rupture,e.g., through chemical or electrical means.

In some embodiments, referred to herein as PCR-Activated Cell Sorting(PACS), a sample including cells is encapsulated in microdroplets andsubjected to PCR conditions, e.g., droplet PCR. In some embodiments, theencapsulated cells are subjected to one or more cell lysing techniques,such as proteinase k digestion or thermal lysis. PCR assays specific tothe cells of interest can cause microdroplets containing the cells ofinterest to become detectably labeled, e.g., fluorescently labeled. Thecells are then recovered by sorting the microdroplets and recoveringtheir contents via microdroplet rupture, e.g., through chemical orelectrical means.

In some embodiments, referred to herein as PCR-Activated Nucleic AcidSorting (PANS), a sample including nucleic acids (e.g., DNA and/or RNA)is encapsulated in microdroplets and subjected to PCR conditions, e.g.,RT-PCR conditions, e.g., droplet PCR (or RT-PCR). PCR, e.g., RT-PCR,assays specific to the nucleic acids of interest can cause dropletscontaining the nucleic acids of interest to become detectably labeled,e.g., fluorescently labeled. The nucleic acids of interest are thenrecovered by sorting the microdroplets and recovering their contents viamicrodroplet rupture, e.g., through chemical or electrical means.

In one aspect of PANS, a method for enriching for a target nucleic acidsequence is provided, wherein the method includes encapsulating a sampleincluding nucleic acids in a plurality of microdroplets, eachmicrodroplet including a first aqueous phase fluid in an immisciblephase carrier fluid; introducing polymerase chain reaction (PCR)reagents and a plurality of PCR primers into the microdroplets;incubating the microdroplets under conditions sufficient for PCRamplification to produce PCR amplification products, wherein theplurality of PCR primers include one or more primers that each hybridizeto one or more oligonucleotides comprised by the target nucleic acidsequence, and wherein the PCR amplification products do not include theentire target nucleic acid sequence; introducing a detection componentinto the microdroplets either before or after the incubating; detectingthe presence or absence of the PCR amplification products by detectionof the detection component, wherein detection of the detection componentindicates the presence of PCR amplification products and the targetnucleic acid sequence; and sorting the microdroplets based on detectionof the detection component, wherein the sorting separates microdropletsincluding the PCR amplification products and the target nucleic acidsequence, when present, from microdroplets which do not include the PCRamplification products and the target nucleic acid sequence; and poolingthe nucleic acid sequences from the sorted microdroplets to provide anenriched pool of target nucleic acid sequences, when present. One ormore of these steps may be performed under microfluidic control.

In some embodiments of the above method, after the incubating, andbefore or after the detecting, the method can include positioning themicrodroplets in an aqueous phase carrier fluid to provide aqueousphase-in-immiscible phase-in aqueous phase microdroplets. In suchembodiments, the sorting may include sorting the aqueousphase-in-immiscible phase-in aqueous phase microdroplets based ondetection of the detection component, wherein the sorting separatesaqueous phase-in-immiscible phase-in aqueous phase microdropletsincluding the PCR amplification products and the target nucleic acid,when present, from aqueous phase-in-immiscible phase-in aqueous phasemicrodroplets which do not include the PCR amplification products andthe target nucleic acid. In such embodiments, the pooling may includepooling the target nucleic acids from the sorted aqueousphase-in-immiscible phase-in aqueous phase microdroplets to provide anenriched pool of the target nucleic acids, when present. One or more ofthese steps may be performed under microfluidic control.

In practicing the subject methods, several variations may be employed.For example, a wide range of different PCR-based assays may be employed,such as quantitative PCR (qPCR). The number and nature of primers usedin such assays may vary, based at least in part on the type of assaybeing performed, the nature of the biological sample, and/or otherfactors. In certain aspects, the number of primers that may be added toa microdroplet may be 1 to 100 or more, and/or may include primers todetect from about 1 to 100 or more different genes (e.g., oncogenes). Inaddition to, or instead of, such primers, one or more probes (e.g.,TaqMan® probes) may be employed in practicing the subject methods.

The microdroplets themselves may vary, including in size, composition,contents, and the like. Microdroplets may generally have an internalvolume of from about 0.001 to 1000 picoliters or more, e.g., from about0.001 picoliters to about 0.01 picoliters, from about 0.01 picoliters toabout 0.1 picoliters, from about 0.1 picoliters to about 1 picoliter,from about 1 picoliter to about 10 picoliters, from about 10 picolitersto about 100 picoliters, or from about 100 picoliters to about 1000picoliters or more. Further, microdroplets may or may not be stabilizedby surfactants and/or particles.

The means by which reagents are added to a microdroplet may varygreatly. Reagents may be added in one step or in multiple steps, such as2 or more steps, 4 or more steps, or 10 or more steps. In certainaspects, reagents may be added using techniques including dropletcoalescence, picoinjection, multiple droplet coalescence, and the like,as shall be described more fully herein. In certain embodiments,reagents are added by a method in which the injection fluid itself actsas an electrode. The injection fluid may contain one or more types ofdissolved electrolytes that permit it to be used as such. Where theinjection fluid itself acts as the electrode, the need for metalelectrodes in the microfluidic chip for the purpose of adding reagentsto a droplet may be obviated. In certain embodiments, the injectionfluid does not act as an electrode, but one or more liquid electrodesare utilized in place of metal electrodes.

Various ways of detecting the absence or presence of PCR products may beemployed, using a variety of different detection components. Detectioncomponents of interest include, but are not limited to, fluorescein andits derivatives; rhodamine and its derivatives; cyanine and itsderivatives; coumarin and its derivatives; Cascade Blue and itsderivatives; Lucifer Yellow and its derivatives; BODIPY and itsderivatives; and the like. Exemplary fluorophores includeindocarbocyanine (C3), indodicarbocyanine (C5), Cy3, Cy3.5, Cy5, Cy5.5,Cy7, Texas Red, Pacific Blue, Oregon Green 488, Alexa fluor-355, AlexaFluor 488, Alexa Fluor 532, Alexa Fluor 546, Alexa Fluor-555, AlexaFluor 568, Alexa Fluor 594, Alexa Fluor 647, Alexa Fluor 660, AlexaFluor 680, JOE, Lissamine, Rhodamine Green, BODIPY, fluoresceinisothiocyanate (FITC), carboxy-fluorescein (FAM), phycoerythrin,rhodamine, dichlororhodamine (dRhodamine), carboxy tetramethylrhodamine(TAMRA), carboxy-X-rhodamine (ROX), LIZ, VIC, NED, PET, SYBR, PicoGreen,RiboGreen, and the like. Detection components may include beads (e.g.,magnetic or fluorescent beads, such as Luminex beads) and the like. Incertain aspects, detection may involve holding a microdroplet at a fixedposition during thermal cycling so it can be repeatedly imaged. Suchrepeated imaging may involve the use of a Megadroplet Array, as shall bedescribed more fully herein. In certain aspects, detection may involvefixing and/or permeabilizing one or more cells in one or moremicrodroplets.

Suitable subjects for the methods disclosed herein include mammals,e.g., humans. The subject may be one that exhibits clinicalpresentations of a disease condition, or has been diagnosed with adisease. In certain aspects, the subject may be one that has beendiagnosed with cancer, exhibits clinical presentations of cancer, or isdetermined to be at risk of developing cancer due to one or more factorssuch as family history, environmental exposure, genetic mutation(s),lifestyle (e.g., diet and/or smoking), the presence of one or more otherdisease conditions, and the like. In certain aspects, the subject may beone that has been diagnosed with a microbial infection, exhibitsclinical presentations of a microbial infection, or is determined to beat risk of developing a microbial infection due to one or more factorssuch as family history, environmental exposure, genetic mutation(s),lifestyle (e.g., diet and/or travel), the presence of one or more otherdisease conditions, and the like. In certain aspects, the subject may beone that has been diagnosed with a viral infection, exhibits clinicalpresentations of a viral infection, or is determined to be at risk ofdeveloping a viral infection due to one or more factors such as familyhistory, environmental exposure, genetic mutation(s), lifestyle (e.g.,diet and/or travel), the presence of one or more other diseaseconditions, and the like.

Microfluidic systems and devices are also provided by the presentdisclosure. In certain aspects, the microfluidic devices include asample loading region, e.g., a cell loading region, to encapsulate,e.g., a cell to be analyzed in a microdroplet; a first chamber influidic communication with the sample loading region, the first chamberhaving a means for adding a first reagent to the microdroplet, and aheating element; a second chamber in fluidic communication with thefirst chamber, the second chamber having a means for adding a secondreagent to the microdroplet, and a heating element, wherein the heatingelement may heat the microdroplet at one or more temperatures; adetection region, in fluidic communication with the second chamber,which detects the presence or absence of reaction products from thefirst or second chamber; and a sorting region, in fluid communicationwith the detection region, which sorts microdroplets based on thedetection of the presence or absence of reaction products from the firstor second chamber. In some embodiments, alternatively or in addition toan “on-chip” sorting region, sorting of the microdroplets may occur“off-chip”. For example, in the case of aqueous phase-in immisciblephase-in aqueous phase double emulsions, an off chip flow cytometrydevice, e.g., a FACS device, may be utilized for sorting.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention may be best understood from the following detaileddescription when read in conjunction with the accompanying drawings.Included in the drawings are the following figures:

FIG. 1 is a simplified depiction of an embodiment of a microfluidicsystem of the instant disclosure. In the depicted system, themicrofluidic system may be used, among a variety of other applications,for detecting and/or genotyping a component of a biological sample. Forexample, as applied to the detection of tumor cells, nucleated bloodcells are encapsulated into individual microdroplets using anencapsulation device (left). The microdroplets are injected with a lysisbuffer and incubated at 37° C. to accelerate cell lysis. They areinjected with PCR mix containing primers targeting characteristiconcogenic mutations (center). The microdroplets are flowed through achannel snaking over zones maintained at 65° C. and 95° C. As themicrodroplets move through the zones, their temperature cycles, asneeded for some PCR reactions. During this PCR reaction, if amicrodroplet contains a genome of a tumor cell with a mutation for whichthe primers are designed to detect, amplification will be initiated,producing a fluorescent output that turns the microdroplet fluorescent.The microdroplets are then optically scanned using flow cytometry andsorted using microdroplet sorting to recover them (right). Themicrodroplets may be stored or used for further analysis, such as beingsubjected to sequencing (e.g., used as input for a next-gen sequencer,or provided to a sequencing facility).

FIG. 2, Panels A-E, depict single cells enclosed in microdroplets, usinga fluorescence assay. Yeast cells (black specks) enter from the far leftand are encapsulated into drops, shown at low (4× objective; Panel A)and high magnification (10× objective; Panel B). The drops are incubatedallowing the yeast to secrete a product (Panel C); this produces afluorescent compound in the drops, so that drops containing efficientproducers quickly become fluorescent (Panel D). The drops are thensorted to extract the most efficient yeast using a microfluidic sorter(Panel E). The scale bars denote 80 mm.

FIG. 3 depicts digital detection of BRAF using a TaqMan® PCR probelabeled with the fluorophore FAM that is complementary to an ampliconfrom a portion of the human BRAF gene. Fluorescent drops indicateamplification of the BRAF gene from purified human genomic DNA, whilenon-fluorescent drops were devoid of the gene.

FIG. 4, Panels A-B, depict a binary PCR reaction to detect CTCs. PanelA: Forward and reverse primers are encapsulated in the drops that targetan oncogenic sequence. If the oncogenic sequence is present, the PCRreaction produces double-stranded PCR products (Panel A, upper),whereas, if it is not, no products are produced (Panel A, lower). Anintercalating stain (e.g., SybrGreen) may also be present in the drop.Panel B: If double-stranded products are produced, the dye intercalatesinto them, becoming fluorescent, and turning the drop fluorescent (PanelB, upper); by contrast, if no double-stranded products are produced, thedye remains non-fluorescent, producing a dim drop (Panel B, lower).

FIG. 5 is an optical microscopy image of massively parallel dropformation in a serial bisection device. DI water that does not containcells is injected from the left. The solution flowing in along the topand bottom arrows is HFE-7500 fluorocarbon oil with a fluorocarbonsurfactant at 2% by weight. After serial bisection, the resulting dropsshown to the far right are 25 μm in diameter.

FIG. 6 is a schematic microfluidic device and data showing procedure fordroplet-based detection of CTCs. Blood cells and rare CTCs areencapsulated in microdrops with lysis buffer containing Proteinase K.The drops are incubated at 55° C. to lyse cells and digest cellularproteins. Drops are then split to a size optimal for imaging, and theProteinase K is heat-inactivated. The drops are then picoinjected withPCR reagents and TaqMan® probes, followed by thermocycling and imagingon a Megadroplet Array. CTCs are identified based on the presence ofCTC-specific transcripts, detected by multiplexed TaqMan® probefluorescence.

FIG. 7 shows relief of cell lysate-mediated inhibition of RT-PCR byproteinase K treatment. Increasing concentrations of cells were eithertreated with proteinase K and lysis buffer or lysis buffer only. Cellswere then incubated at 55° C. followed by 95° C. Whole cell lysates wereadded directly to RT-PCR reactions at several drop relevantconcentrations. Strong relief of lysate inhibition on PCR was seen atfinal cell concentrations of 1 cell per 200 pL in Proteinase K treatedlysates but not in lysis buffer only lysates. PCR products arevisualized on an ethidium bromide stained agarose gel.

FIG. 8, Panels 1-3, show an integrated microfluidic system for cellencapsulation/dilution, lysis and drop splitting (center image). Panel1: Co-flow module relies on laminar flow of Proteinase K containinglysis buffer and cell suspension solutions to encapsulate cells in dropswithout premature lysis or mixing of cells prior to drop formation; alaminar flow boundary is just visible between the cell and lysis bufferstreams. Panel 2: Drops containing cells flow through a 55° C.incubation channel for 20 minutes to lyse cells and digest inhibitoryproteins. Panel 3: Drops are split to allow for efficient picoinjectionof 2×RT-PCR reagents and imaging on the droplet array

FIG. 9, Panels A-C, show TaqMan® RT-PCR in drops followingpicoinjection. Drops containing a limiting dilution of total RNA fromthe prostate cancer cell line PC3 were injected with an equal volume of2×RT-PCR reagents and a TaqMan® probe targeting EpCAM, (Panel A).Following picoinjection, drops were thermocycled and imaged forfluorescence, (Panel B). The number of fluorescent drops was found to bein agreement with the prediction of a Poisson distribution,demonstrating adequate sensitivity to detect single transcript moleculesin drops. Panel C: To further confirm the results, the drops from PanelB were chemically ruptured and their contents run on an agarose gel toobserve the presence of PCR products in negative control drops that wereinjected without RT-PCR enzymes (−) and experimental drops that receivedboth RT and Taq (+). Both control reactions performed in a tube with nopicoinjection and picoinjected reactions produced bands of similarintensity, demonstrating that the reaction efficiency was comparable.White stars mark picoinjected drops.

FIG. 10 shows detection of EpCAM transcripts from droplet encapsulatedMCF7 breast cancer cells. Using the device depicted in FIG. 8, Panels1-3, MCF7 cells were encapsulated in drops, lysed and drops were split.Lysate containing drops were then picoinjected with RT-PCR reagents andTaqMan® probes. Drops were then thermocycled and imaged forfluorescence. Brightfield and fluorescent channels are shown merged.

FIG. 11 depicts digital droplet RT-PCR multiplexing with TaqMan® probes.Limiting dilutions of total RNA from both Raji cells (B-lymphocytes) andPC3 prostate cancer cells were encapsulated in drops together withRT-PCR reagents and TaqMan® probes specific to CD45 (blue), CD44 (red)and EpCAM (green). Orange drops indicate the presence of both CD44 andEpCAM transcripts detected by a multiplex reaction. Other probemultiplexing combinations have also been seen (data not shown).Fluorescent channels are shown individually as a magnified inset for thedashed box region.

FIG. 12, Panels A-C, show a schematic illustration of a device forperforming multiplexed qPCR analysis on cells individually. The deviceconsists of an array of about 10 million traps indented into a PDMSchannel that sits above a thermal system (Panel A). The height of themicrofluidic channel is smaller than the diameter of the drops, causingdrops to adopt a flattened pancake shape. When a drop flows over anunoccupied indentation, it adopts a lower, more energetically favorable,radius of curvature, leading to a force that pulls the drop entirelyinto the trap (Panel B). By flowing drops as a close pack, it is ensuredthat all traps on the array are occupied, as illustrated in Panel C. Theentire device is thermal cycled and imaged between cycles using amicroarray scanner.

FIG. 13 depicts a Megadroplet Array for multiplexed qPCR analysis, ofthe type depicted in FIG. 12, Panels A-C. Drops are pipetted and sealedin a clear glass/epoxy chamber and fixed in place using amicrofabricated well array (top). The entire chip is clamped to a metalblock and thermocycled using Peltier heaters under the copper blocks.Thermometers, a heat sink, a fan (top), and digital controllers are usedto regulate and cycle the temperature (bottom). Amplification ismonitored in real time by imaging the array through the transparentplates that make up the top of the device.

FIG. 14, Panels A-B, depict the use of a one-color flow-cytometer usedto detect PCR amplification products in drops, via fluorescence. PanelA: Schematic of detector, consisting of a 488 nm laser directed into theback of an objective, and focused onto a microfluidic channel throughwhich the droplets flow. The laser excites fluorescent dyes within thedrops, and any emitted light is captured by the objective and imagedonto a photomultiplier tube (PMT) after it is filtered through adichroic mirror and 520 f 5 nm band pass filter. Panel B: The dropsappear as peaks in intensity as a function of time, as shown by theoutput voltage of a PMT, which is proportional to the intensity of theemitted light, as a function of time for detected fluorescent drops.

FIG. 15, Panels A-C, show a schematic of device setup. Panel A: Drops,spacer oil, and 1 M NaCl are introduced to the PDMS device via syringepumps. The picoinjection fluid is introduced using an air pressurecontrol pump. Electrodes from the high voltage amplifier are connectedto a wire submerged in the picoinjection fluid and to the metal needleof the syringe containing the 1 M NaCl “Faraday Mote.” Panel B: Amagnified view of the droplet spacer and picoinjection site. Panel C:Further magnified view of the picoinjection site showing the fluid bulgeat the injection orifice.

FIG. 16, Panels A-B, show bright field microscopy images of thepicoinjection site. In the absence of an electric field (Panel A),surfactants prevent coalescence with the injection fluid and a distinctboundary is visible at the droplet/injection fluid interface. When theelectric field is applied, the boundary disappears and reagent isinjected as the droplet passes (Panel B).

FIG. 17, Panels A-C, show the volume fraction increase (Vf) of drop sizeafter injection for (Panel A) 100 mM, (Panel B) 50 mM, and (Panel C) 25mM injection fluids. A stronger electric field more readily ruptures theoil/water interfaces allowing injection over a larger length of thepassing droplets, and larger injection volumes. Higher molarities ofdissolved electrolytes produce stronger electric fields at the injectionsite for a given voltage, also increasing injection volume. The errorbars represent 1 standard deviation in either direction for >1200 dropssampled at each point.

FIG. 18 is a heat map showing injection volume as a function of appliedvoltage and the molarity of dissolved NaCl in the injection fluid.Arrows/ticks indicate data points. The injection volume can be adjustedin the range of 0-36 pL with a resolution of ˜2.6 pL 5 (4% Vf) with 100Vincrements of the applied signal. The largest injected volumes were 3000V with the 100 mM fluid. Increasing electric field above this allows forelectrowetting, causing drops to spontaneously form at the picoinjector,adversely affecting injection efficacy and consistency.

FIG. 19 shows ethidium bromide stained 2% agarose gel. Total RNAisolated from an MCF7 human cell line was encapsulated in drops andpicoinjected with an RT-PCR reaction mixture either with (+) or without50 (−) reverse transcriptase (RT) and Taq DNA polymerase. Non-emulsifiedcontrol reactions were performed in parallel. Only reactions receivingenzyme generated the expected 100 bp amplicon. Both positive control andpicoinjected reactions produced PCR products, demonstrating that theelectric field generated during picoinjection is 55 biologicallycompatible with DNA, reverse transcriptase, and Taq.

FIG. 20, Panels A-B, show adding reagents via multiple dropletcoalescence. Panel A: A schematic of a microfluidic device for addingreagents via multiple droplet coalescence. The reagent to add isintroduced from below, along with oil, into a very small drop maker.This leads to the production of a train of very small drops at a highfrequency. The drops to which the reagent is to be added are injected,spaced by oil, from the left and then the streams combine where thechannel intersects with the outlet of the tiny drop maker. Because thereagent drops are much smaller than the target drops, they areintroduced at a high rate frequency, and so many (tens or more) of thesedrops are injected for every one target drop. Due to their small sizethey flow faster than the larger drops and collect behind them so that,by the time the reach the electrode channels they are in contact and canbe coalesced by the electric field. Panel B: Close-up of the coalescenceregion in such a microfluidic device. Drops flow from left to the right.A train of tiny droplets form behind the droplet to which they are to beadded. Once the tiny droplets and the droplet pass through thecoalescence region, the electrodes cause the tiny droplets to merge intothe droplet. The resulting output on the right is a droplet thatcontains the reagent(s) that were present in the tiny droplets.

FIG. 21 shows a schematic of a microfluidic device whereby amicrodroplet may be purified. That is, a majority of the fluid in thedrop is replaced it with a purified solution, without removing anydiscrete reagents that may be encapsulated in the drop, such a cells orbeads. The microdroplet is first injected with a solution to dilute anyimpurities within it. The diluted microdroplet is then flowed through amicrofluidic channel on which an electric field is being applied usingelectrodes. Due to the dielectrophoretic forces generated by the field,as the cells or other discrete reagents pass through the field they willbe displaced in the flow. The drops are then split, so that all theobjects end up in one microdroplet. Accordingly, the initialmicrodroplet has been washed, in that the contaminants may be removedwhile the presence and/or concentration of discrete reagents, such asbeads or cells, that may be encapsulated within the droplet aremaintained in the resulting microdroplet.

FIG. 22, Panels A-B, show sorting. Droplets enter from the right andflow to the left, passing by the electrodes. The drops are thus sortedon the presence (Panel A; droplets flow into the top output) or absenceof a particular property (Panel B; droplets flow into the bottomoutput).

FIG. 23 shows a schematic of a coalescence process, starting with theformation of double emulsions (E2) from a reinjected single emulsion(E1) in a hydrophilic channel (top, left). These are turned into tripleemulsions (E3) at a hydrophobic junction (bottom, left), which are thencoalesced using an electric field into an inverted E2 (E2′, bottom,right).

FIG. 24, Panels A-D, show microscope images of (a) double emulsions (E2)formation, (b) triple emulsion (E3) formation, (c) E3 coalescence, and(d) the final inverted E2 (E2′) products. The scale bar applies to allimages.

FIG. 25, Panels A-B, show two fast-camera time series showing E3coalescence into E2′. The oil shell of the inner E1 is false-coloredblue.

FIG. 26, Panels A-C, show microfluidic devices and digital RT-PCRworkflow used in the study of Example 5. (A) Drops containing RNA andRT-PCR reagents are created with a microfluidic T-junction and carrieroil. Brightfield microscopy images of the drop formation are shownbelow, the middle image showing the generation of one population ofdrops from a single reaction mixture, and the lower the generation oftwo populations from two mixtures. (B) After formation, the drops arepicoinjected with reverse transcriptase using a picoinjection channeltriggered by an electric field, applied by an electrode channelimmediately opposite the picoinjector. (C) The picoinjected drops arecollected into a tube, thermocycled, and imaged with a fluorescentmicroscope.

FIG. 27, Panels A-C, show digital RT-PCR TaqMan® assays in microfluidicdrops following picoinjection of reverse transcriptase. (A) ControlRT-PCR reactions containing PC3 cell total RNA were emulsified on aT-junction drop maker, thermocycled, and imaged. FAM (green)fluorescence indicates TaqMan® detection of an EpCAM transcript and Cy5(red) indicates detection of CD44 transcripts. Brightfield images (BF)of the same drops are shown in the image panel on the far right. (B)RT-PCR reactions lacking reverse transcriptase were emulsified on aT-junction drop maker and subsequently picoinjected with reversetranscriptase. Picoinjection fluid is pictured as dark gray in theschematic diagram on the left. Brightfield images demonstrate that thedrops roughly doubled in size after picoinjection. (C) RT-PCR reactionssubjected to picoinjection omitting the reverse transcriptase show noTaqMan® signal for EpCAM and CD44, demonstrating the specificity of theTaqMan® assay. The red arrows indicate the direction of emulsion flow inthe illustrations. Scale bars=100 μm.

FIG. 28, Panels A-B, show a comparison of digital RT-PCR detection ratesbetween control drops and drops that were picoinjected with reversetranscriptase. (A) Scatter plots of FAM and Cy5 drop intensities for acontrol sample (left) and picoinjected sample (right). The gatingthresholds used to label a drop as positive or negative for TaqMan®signal are demarcated by the lines, and divide the scatter plot intoquadrants, (−,−), (−,+), (+,−), (+,+). (B) The bar graph shows theaverage TaqMan® positive drop count with picoinjection relative to thenormalized count for CD44 and EpCAM TaqMan® assays for controlpopulations. The data represent the average of four independentexperimental replicates.

FIG. 29, Panels A-B, shows that picoinjection enables analysis ofdiscrete drop populations. (A) Non-picoinjected drops. Control RT-PCRreactions containing mixed PC3 cell total RNA and Raji cell total RNAwere emulsified with a T-junction drop maker, thermocycled, and imaged.Merged FAM and HEX fluorescent images are shown with FAM (green)fluorescence indicating TaqMan® detection of an EpCAM transcript and HEX(red) indicating the presence of PTPRC transcripts. The yellow dropsindicate the presence of multiplexed TaqMan® assays, where EpCAM andPTPRC transcripts were co-encapsulated in the same drop. The brightfieldimages (BF) are shown in the panel on the right. (B) Picoinjected drops.A double T-junction drop maker simultaneously created two populations ofdrops that were immediately picoinjected. One drop maker created dropscontaining only Raji cell RNA, and the other drops containing only PC3cell RNA. Both drop types initially lack reverse transcriptase, which isadded via picoinjection just downstream of the drop makers. Theoverwhelming majority of drops display no multiplexing, demonstratingthat transfer of material during picoinjection is very rare. The redarrows indicate the direction of emulsion flow in the illustrations.Scale bars=100 μm.

FIG. 30, Panels A-B, shows a dual transcript detection analysis,indicating minimal cross-contamination during picoinjection. (A) Scatterplots of FAM and HEX drop intensities for a co-encapsulated controlsample (left) and dual population picoinjected sample (right). Usingthis analysis, large numbers of TaqMan® multiplexed drops wereidentified in the co-encapsulated controls that were virtually absent inthe dual population picoinjected drops (upper right quadrants of gatedscatter plots). (B) A bar graph of different bright drop populationsrelative to the total bright count for co-encapsulation control and fordual population picoinjection. The data represent the average of threeexperimental replicates.

FIG. 31 Panels A-B, shows that dual populations of RNA drops can bestored offline and picoinjected at a later time. (A) An emulsion wasmade consisting of two populations of drops, one containing RNArecovered from Raji cells, and the other from PC3 cells. The drops werecollected into a syringe, incubated off chip, and then re-introducedinto a microfluidic device to picoinject. The drops were then collected,thermocycled, and imaged. These drops are somewhat more polydisperse anddisplayed higher multiplexing rates (1%) than the drops picoinjected onthe same device on which they were formed, which is most likely due tomerger of some of the drops during incubation and reinjection. Theability to reinject emulsions following incubation to add reagents maybe important for numerous droplet-based molecular biology assays. (B)Brightfield images of picoinjected emulsions. Scale bars=100 μm.

FIG. 32 shows an embodiment of a single cell RT-PCR microfluidic deviceas described herein.

FIG. 33 shows the effect of including ridge structures in a microfluidicdevice channel downstream of a droplet forming junction. A T-junctiondrop maker without ridges is shown to the left. As the flow rate ratiois increased, the drop maker stops forming drops and instead forms along jet. This is due to the jet wetting the channel walls and adhering,preventing the formation of drops. On the right, a similar T-junction isshown with ridge structures. The ridges trap a suitable phase, e.g., ahydrophobic oil phase, near the walls, making it difficult for theaqueous phase to wet. This allows the device to form drops at muchhigher flow rate ratios before it eventually wets at R=0.9. This showsthat inclusion of the ridges allows the drop maker to function over amuch wider range than if the ridges are omitted. The channel widths are30 microns and the peaks of the ridges are about 5-10 microns. The topand bottom sets of images correspond to experiments performs withdifferent microfluidic devices.

FIG. 34 provides a flow diagram showing a general fabrication scheme foran embodiment of a liquid electrode as described herein.

FIG. 35 provides a sequence of three images taken at different times asan electrode channel is being filled with salt water (time courseproceeds from left to right; Panels A-C). The salt water is introducedinto the inlet of the channel and pressurized, causing it to slowly fillthe channel. The air that is originally in the channel is pushed intothe PDMS so that, by the end, it is entirely filled with liquid.

FIG. 36 shows electric field lines simulated for various liquidelectrode configurations. The simulations are of positive and groundelectrodes showing equipotential lines for three different geometries.

FIG. 37 provides two images of a droplet merger device that merges largedrops with small drops utilizing liquid electrodes. To merge the drops,an electric field is applied using a salt-water electrode. When thefield is off, no merger occurs (right) and when it is on, the dropsmerge (left).

FIG. 38 provides two different views of a three dimensions schematicshowing a device which may be used to encapsulate single emulsions indouble emulsions. It includes a channel in which the single emulsionsare introduced, which channel opens up into a large channel in whichadditional aqueous phase is added. This focuses the injected dropsthrough an orifice, causing them to be encapsulated in oil drops andforming water-in-oil-in-water double emulsions.

FIG. 39 provides two schematics of PDMS slabs that may be used toconstruct a double emulsification device. The slab on the left haschannels with two heights—short channels for the droplet reinjection andconstriction channels (see previous Figure) and tall channels for theaqueous phase and outlets. The slab on the right has only the tallchannels. To complete the device, the slabs are aligned and sealedtogether so that the channels are facing. The devices are bonded usingplasma oxidation.

FIG. 40 provides a microscope image of a double emulsification deviceencapsulating a reinjected single emulsions in double emulsions. Thereinjected single emulsions enter from above and are encapsulated in theconstriction shown in the center of the device. They then exit as doubleemulsions, four of which are shown towards the bottom of the device.

FIG. 41 provides fluorescent microscope images of fluorescent doubleemulsions. The image on the left shows double emulsions formed byshaking the fluids, which results in a large amount of polydispersityand a small number of drops of the appropriate size for FACS sorting.The image on the right shows double emulsions made with the microfluidicprocess disclosed herein, which are much more monodisperse.

FIG. 42 provides a histogram of the drop areas for shaken vs.device-created double emulsions. The device-created double emulsions aremuch more monodisperse, as demonstrated by the peak.

FIG. 43 shows FACS fluorescence and scattering data for microfluidicdevice generated double emulsions according to the present disclosure.The upper plot shows the intensity histogram of the population asmeasured with the FITC channel (˜520 nm) of the FACS. The plots belowshow the forward and side scattering of the drops, gated according toFITC signal.

FIG. 44 shows FACS fluorescence and scattering data for shaken doubleemulsions. The upper plot shows the intensity histogram of thepopulation as measured with the FITC channel (˜520 nm) of the FACS. Theplots below show the forward and side scattering of the drops, gatedaccording to FITC signal.

FIG. 45 provides a histogram of droplet intensity as read out with theFACS (FITC channel) for four different concentrations of encapsulateddye. The dye is composed of fluorescently-labeled BSA.

FIG. 46 shows the results of an experiment designed to test thedetection rate of the FACS-run drops. Two populations of drops werecreated, one with labeled BSA fluorescent at 520 nm, and another withBSA fluorescent at 647 nm. The two populations were then mixed indefined ratios and the samples were run on FACS. The measured ratio wasfound to agree with the known ratio, demonstrating that the FACSmeasurements are accurate over this range.

FIG. 47 shows emulsions containing three different concentrations ofDNA. All drops contain TaqMan® probes for the DNA target, but the targetis encapsulated at limiting concentration, so that only the drops thatget a target undergo amplification. When the target concentration isreduced, the fraction of fluorescent drops goes down. The lower plotsshow the drops after being encapsulated in double emulsions and screedon FACS.

FIG. 48 shows emulsions containing three concentrations of DNA lowerthan those in the previous Figure. All drops contain TaqMan® probes forthe DNA target, but the target is encapsulated at limitingconcentration, so that only the drops that get a target undergoamplification. When the target concentration is reduced, the fraction offluorescent drops goes down. The lower plots show the drops after beingencapsulated in double emulsions and screed on FACS.

FIG. 49 shows emulsions as for FIGS. 47 and 48 at the lowest DNAconcentration of the three Figures. The lower plot shows the drops afterbeing encapsulated in double emulsions and screed on FACS.

FIG. 50 shows a plot of the detected number of positives by FACSanalysis of double emulsions plotted versus the number of positivesdetected by imaging the drops before double emulsification using afluorescent microscope. The results agree with one another over the twodecades tested.

FIG. 51 provides a plot showing the fraction of drops that are positiveas a function of the log-2 concentration. As the concentration of DNAgoes up, more drops become fluorescent because more of them contain atleast a single molecule.

FIG. 52 provides images showing drops in which a TaqMan® PCR reactionhas been performed with encapsulated Azospira. The upper imagescorrespond to a reaction in which a 110 bp amplicon was produced,whereas the lower images correspond to a 147 bp amplicon.

FIG. 53 shows a picture of a gel showing bands corresponding to theamplicons of two TaqMan® PCR reactions, one for a 464 bp amplicon andone for a 550 bp amplicon.

FIG. 54 shows a picture of a gel validating that PCR reactions can bemultiplexed by adding multiple primer sets to a sample containingbacteria.

FIG. 55 shows results for the PCR amplification of Azospira amplicons(left) and FACS analysis of Azospira containing double emulsions(right).

FIG. 56, Panels a-d, show a workflow for PCR-activated cell sortingaccording to certain embodiments. Although specific cell types andreagents are listed, these are for purposes of illustration only and arenot intended to be limiting. FIG. 56, Panels a and b, show that, e.g.,Raji and DU145 cells are isolated into aqueous microdroplets in anoil-based emulsion and lysed. Only DU145 cells express vimentin mRNA andhave genetic mutations in RB1 and CDKN2A genes. FIG. 56, Panel c, showsa microfluidic chip processing the cells, readying the lysate for PCR.Single-cell TaqMan PCR reactions targeting vimentin mRNA arethermocycled and droplets are sorted based on positive TaqMan probefluorescence. FIG. 56, Panel d, shows cell lysate being recovered fordownstream nucleic acid analysis following microfluidic droplet sorting.

FIG. 57, Panels a-b, show single-cell vimentin TaqMan assays that arespecific for DU145 cancer cells according to certain embodiments. FIG.57, Panel a, depicts merged brightfield and fluorescence images showingamplified vimentin TaqMan probe (red), calcein violet DU145 (blue) andcalcein green Raji (green) lysate in droplets. The presence of apurple-violet color indicates droplets where both DU145 calcein violetstain and HEX from the vimentin TaqMan probe were detected. Individualfluorescence channels from the dashed region are shown. Scale bar is 100nm. FIG. 57, Panel b, shows Vimentin TaqMan detection rates ofindividual DU145 and Raji cells processed with the single-cell RT-PCRmicrofluidic workflow. Data was compiled from replicate experimentsanalyzed with a MATLAB script.

FIG. 58, Panels a-d, depicts correlation analysis between calcein violetand green cell stains according to certain embodiments.

FIG. 59, Panels a-c, depicts ultrahigh-throughput detection andPCR-activated sorting of droplets according to certain embodiments. FIG.59, Panel a, shows a photograph of a dielectrophoretic microfluidicsorter. Reinjected emulsion entered the device from the left and wasinterrogated for fluorescence at the laser spot. A voltage was appliedto the sorting electrode when a droplet was positive for both calceinand HEX above the specified thresholds. This pulled the specifieddroplets into the lower channel for collection. Scale bar is 100 nm.FIG. 59, Panel b, shows a Scatterplot diagram of single-cell RT-PCRsorted droplets showing the calcein violet cell stain fluorescence usedto mark Raji and DU145 cells on the x axis and HEX fluorescence from theTaqMan positive reactions on the y axis. Dashed red lines indicate wherethe sorting thresholds were applied. Only droplets in the upper rightquadrant were selected for sorting. This PACS data was generated from aninitial 80% Raji and 20% DU145 heterogeneous cell suspension. FIG. 59,Panel c, shows imaged pre-sorted and sorted droplets to evaluate sortingefficiency. Arrowheads in the pre-sorted emulsion image point to twodroplets positive for both calcein and HEX. The rest of the droplets areeither empty or only calcein positive. Nearly all of the dropletsfollowing sorting are positive for both calcein and HEX.

FIG. 60 depicts a scatterplot of HEX and calcein fluorescence accordingto certain embodiments. FIG. 60 shows that 95.8% of positively-sorteddroplets had significant calcein and HEX fluorescence.

FIG. 61, Panels a-b, show Sanger sequencing of PACS enriched genomic DNAaccording to certain embodiments. FIG. 61, Panel a, shows a portion ofthe RB1 locus was amplified from genomic DNA isolated from individualcell lines and Sanger sequenced as a control (top two sequences). Rajicell RB1 encodes for a lysine at amino acid position 715 (black box).DU145 genomic DNA has a nonsense mutation at this position (red box).Sequencing of genomic DNA amplified from droplets prior tovimentin-positive PACS sorting (Pre-sorted) produces a Raji cellsequence with lysine at position 715. This is expected based on theinitial encapsulation of a 90% Raji cell and 10% DU145 cell suspension.Following vimentin-positive droplet sorting (Vimentin+PACS), sequencingshows that the genomic DNA is dramatically enriched for theDU145-specific stop codon. (SEQ ID NO:25 on left, SEQ ID NO:26 onright).

FIG. 61, Panel b, shows sequencing of CDKN2A amplicons from control cellgenomic DNA (top two sequences) Amino acid 84 is mutated from anaspartic acid to a tyrosine in DU145 cells (red box). Sequencing of thepre-sorted single-cell RT-PCR emulsion DNA yields a Raji-specificaspartic acid. Following vimentin-positive PACS sorting, the genomic DNAis enriched for tyrosine encoding sequence. Arrows indicate the positionof the SNPs. (SEQ ID NO: 27 on left, SEQ ID NO:28 on right).

FIG. 62, Panels a-b, show quantitative analysis of PACS genomeenrichment with next-generation sequencing according to certainembodiments. Analysis of RB1 and CDKN2A genomic loci for the presence ofDU145-specific SNPs. Sequencing libraries from RB1 and CDKN2A ampliconswere generated using Nextera XT reagents. FIG. 62, Panel a, depictsquantitative analysis of RB1 sequence reads demonstrated that theDU145-specific nonsense mutation, AAG to TAG, was found in 6.2% of thesequence reads generated from pre-sorted cell lysate. Following PACSsorting (Vim+PACS) the presence of this mutation relative to theRaji-specific codon was enriched to 87.7%. FIG. 62, Panel b, shows thatsimilar data was obtained upon sequence analysis of CDKN2A ampliconsgenerated from pre-sorted and Vim+PACS sorted cell lysate. The DU145specific missense mutation, GAC to TAC, went from including 13.5% of thesequence reads to 74.2% of the sequence reads upon PACS enrichment. Morethan 15,000 sequence reads were analyzed for each of the 4 samples.

FIG. 63, Panels a-b, show mRNA expression analysis following PACSenrichment according to certain embodiments. FIG. 63, Panel a, depictsqRT-PCR amplification curves from GAPDH or CD9 performed on cell lineisolated total RNA control samples. CD9 was expressed significantlyhigher in DU145 cells than in Raji cells. FIG. 63, Panel b shows RNAfrom pre-sorted and vimentin-positive PACS (Vim sorted) droplets wasanalyzed for CD9 expression following normalization of input levels withGAPDH. CD9 was only detected in the vimentin-positive sorted dropletsindicating that PACS enriched for DU145 expressed transcripts. Threereplicate amplification curves are shown for each qRT-PCR experiment.

FIG. 64, Panels a-f, show PACS workflow applied to a model microbialsystem according to certain embodiments. FIG. 64, Panel a, depicts amicrobial sample including, e.g., K-12 E. coli harboring wild type TolAand a spike-in variant (ΔTolA) is created from growth cultures. FIG. 64,Panel b, shows the sample of FIG. 64, Panel a, encapsulated togetherwith PCR reagent to form a single emulsion. FIG. 64, Panel c-d, depictscollecting and thermal cycling the emulsion with PCR-positive dropletsexperiencing an increase in TaqMan fluorescence. FIG. 64, Panel e,depicts DEP sorting for bright drops. FIG. 64, Panel f, depictsrupturing the drops to release genomic content which is sequenced toverify sorting efficacy.

FIG. 65, Panels a-b, depict TaqMan PCR detection of TolA gene in E. colibacteria. E. coli bacteria are encapsulated with PCR reagents indroplets and are thermalcycled. FIG. 65, Panel a (upper), depicts thatdrops containing bacteria with the TolA gene are bright, whereas this isabsent in FIG. 65, Panel a (lower), which depicts E. coli without thisgene. FIG. 65, Panel b, shows the dependency of the fraction of loadingdrops which are bright versus the poisson loading ratio. The differentcurves represent different calculated curves if the E. coli lysis factork was varied.

FIG. 66 depicts droplet size distribution according to certainembodiments. In this example, single emulsion droplet diameters werequantified using ImageJ, with a total of 1200 drops measured for allconcentrations of bacteria. The average drop volume was calculated to be34.7 pL.

FIG. 67 depicts a DEP droplet sorting device according to certainembodiments.

FIG. 67, upper, shows the device layout, with the salt “moat” insulatingthe drops from any stray electric fields potentially originating fromthe salt electrode. This device includes a reinjection junction, FIG.67, left, at which the reinjected emulsion is spaced out, as well as asorting junction, FIG. 67, middle, which is, e.g., where detection andsorting occurs. FIG. 67, right, shows positive and negative dropletsorting events.

FIG. 68, Panels a-b, depicts droplet detection and sorting of dropsaccording to certain embodiments. FIG. 68, Panel a, depicts a PMTtimetrace of recorded signals from an optical droplet detection setup.There is a clear peak at 32.5 ms, which corresponds to a bright dropthat is sorted. FIG. 68, Panel b, shows fluorescence images ofthermalcycled drops before and after DEP sorting.

FIG. 69, Panels a-b, illustrate sequencing verification and genomeenrichment according to certain embodiments. FIG. 69, Panel a, depictsan electropherogram of the LpoA gene and its mutant counterpart afterSanger sequencing LpoA from sorted bacterial genomes. FIG. 69, Panel b,shows sequencing results, with enrichments for the TolA/ALpoA bacterialstrain for both spike-in ratios. (SEQ ID NO:29 on left, SEQ ID NO:30 onright).

FIG. 70, Panels a-c, provides a schematic of a microfluidic doubleemulsion FACS analysis according to certain embodiments. A coaxialflow-focusing device, e.g., as shown in FIGS. 38-40, is utilized toencapsulate drops in double emulsions for subsequent FACS analysis.

FIG. 71 provides a schematic of an embodiment of a PCR-Activated NucleicAcid Sorting method according to the present disclosure.

DETAILED DESCRIPTION

The methods described herein, referred to as PCR-Activated Sorting(PAS), allow nucleic acids contained in biological systems to be sortedbased on their sequence as detected with PCR. The nucleic acids can befree floating or contained within living or nonliving structures,including particles, viruses, and cells. The nucleic acids can include,e.g., DNA or RNA. Systems and devices for use in practicing methods ofthe invention are also provided.

Before the present invention is described in greater detail, it is to beunderstood that this invention is not limited to particular embodimentsdescribed, and as such may, of course, vary. It is also to be understoodthat the terminology used herein is for the purpose of describingparticular embodiments only, and is not intended to be limiting, sincethe scope of the present invention will be limited only by the appendedclaims.

Where a range of values is provided, it is understood that eachintervening value, to the tenth of the unit of the lower limit unlessthe context clearly dictates otherwise, between the upper and lowerlimits of that range is also specifically disclosed. Each smaller rangebetween any stated value or intervening value in a stated range and anyother stated or intervening value in that stated range is encompassedwithin the invention. The upper and lower limits of these smaller rangesmay independently be included or excluded in the range, and each rangewhere either, neither or both limits are included in the smaller rangesis also encompassed within the invention, subject to any specificallyexcluded limit in the stated range. Where the stated range includes oneor both of the limits, ranges excluding either or both of those includedlimits are also included in the invention.

Unless defined otherwise, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although any methods andmaterials similar or equivalent to those described herein can be used inthe practice or testing of the present invention, some potential andexemplary methods and materials may now be described. Any and allpublications mentioned herein are incorporated herein by reference todisclose and describe the methods and/or materials in connection withwhich the publications are cited. It is understood that the presentdisclosure supersedes any disclosure of an incorporated publication tothe extent there is a contradiction.

It must be noted that as used herein and in the appended claims, thesingular forms “a”, “an”, and “the” include plural referents unless thecontext clearly dictates otherwise. Thus, for example, reference to “amicrodroplet” includes a plurality of such microdroplets and referenceto “the microdroplet” includes reference to one or more microdroplets,and so forth.

It is further noted that the claims may be drafted to exclude anyelement which may be optional. As such, this statement is intended toserve as antecedent basis for use of such exclusive terminology as“solely”, “only” and the like in connection with the recitation of claimelements, or the use of a “negative” limitation.

The publications discussed herein are provided solely for theirdisclosure prior to the filing date of the present application. Nothingherein is to be construed as an admission that the present invention isnot entitled to antedate such publication by virtue of prior invention.Further, the dates of publication provided may be different from theactual publication dates which may need to be independently confirmed.To the extent such publications may set out definitions of a term thatconflict with the explicit or implicit definition of the presentdisclosure, the definition of the present disclosure controls.

As will be apparent to those of skill in the art upon reading thisdisclosure, each of the individual embodiments described and illustratedherein has discrete components and features which may be readilyseparated from or combined with the features of any of the other severalembodiments without departing from the scope or spirit of the presentinvention. Any recited method can be carried out in the order of eventsrecited or in any other order which is logically possible.

Methods

As summarized above, aspects of the present disclosure include methodsfor the detection and sorting of components from biological samples.Aspects include methods for the detection, quantification, and/orgenotyping of cells, e.g. normal mammalian cells (e.g., non-tumorcells), tumor cells, CTCs, or microbial cells. Additional embodiments ofinterest include PCR-based sorting of viral particles and PCR-basedsorting of nucleic acids from a heterogeneous population of nucleicacids.

As used herein, the term “biological sample” encompasses a variety ofsample types obtained from a variety of sources, which sample typescontain biological material. For example, the term includes biologicalsamples obtained from a mammalian subject, e.g., a human subject, andbiological samples obtained from a food, water, or other environmentalsource, etc. The definition encompasses blood and other liquid samplesof biological origin, as well as solid tissue samples such as a biopsyspecimen or tissue cultures or cells derived therefrom and the progenythereof. The definition also includes samples that have been manipulatedin any way after their procurement, such as by treatment with reagents,solubilization, or enrichment for certain components, such aspolynucleotides. The term “biological sample” encompasses a clinicalsample, and also includes cells in culture, cell supernatants, celllysates, cells, serum, plasma, biological fluid, and tissue samples.“Biological sample” includes cells; biological fluids such as blood,cerebrospinal fluid, semen, saliva, and the like; bile; bone marrow;skin (e.g., skin biopsy); and antibodies obtained from an individual.

As described more fully herein, in various aspects the subject methodsmay be used to detect a variety of components from such biologicalsamples. Components of interest include, but are not necessarily limitedto, cells (e.g., circulating cells and/or circulating tumor cells),viruses, polynucleotides (e.g., DNA and/or RNA), polypeptides (e.g.,peptides and/or proteins), and many other components that may be presentin a biological sample.

“Polynucleotides” or “oligonucleotides” as used herein refer to linearpolymers of nucleotide monomers, and may be used interchangeably.Polynucleotides and oligonucleotides can have any of a variety ofstructural configurations, e.g., be single stranded, double stranded, ora combination of both, as well as having higher order intra- orintermolecular secondary/tertiary structures, e.g., hairpins, loops,triple stranded regions, etc. Polynucleotides typically range in sizefrom a few monomeric units, e.g. 5-40, when they are usually referred toas “oligonucleotides,” to several thousand monomeric units. Whenever apolynucleotide or oligonucleotide is represented by a sequence ofletters (upper or lower case), such as “ATGCCTG,” it will be understoodthat the nucleotides are in 5′→3′ order from left to right and that “A”denotes deoxyadenosine, “C” denotes deoxycytidine, “G” denotesdeoxyguanosine, and “T” denotes thymidine, “I” denotes deoxyinosine, “U”denotes uridine, unless otherwise indicated or obvious from context.Unless otherwise noted the terminology and atom numbering conventionswill follow those disclosed in Strachan and Read, Human MolecularGenetics 2 (Wiley-Liss, New York, 1999).

The terms “polypeptide,” “peptide,” and “protein,” used interchangeablyherein, refer to a polymeric form of amino acids of any length. NH₂refers to the free amino group present at the amino terminus of apolypeptide. COOH refers to the free carboxyl group present at thecarboxyl terminus of a polypeptide. In keeping with standard polypeptidenomenclature, J. Biol. Chem., 243 (1969), 3552-3559 is used.

In certain aspects, methods are provided for counting and/or genotypingcells, including normal cells or tumor cells, such as CTCs. A feature ofsuch methods is the use of microfluidics.

FIG. 1 presents a non-limiting, simplified representation of one type ofa microfluidics system and method of the present disclosure. Theparticular application depicted in FIG. 1 may be utilized in thedetection and/or genotyping of cells, e.g., tumor cells, from abiological sample. In one such method, nucleated blood cells may beobtained from a biological sample from a subject. The nucleated bloodcells are encapsulated into individual microdroplets using anencapsulation device (left). The microdroplets may then be injected witha lysis buffer and incubated at conditions that accelerate cell lysis(e.g., at 37° C.). The microdroplets may be injected with a PCR mix thatincludes one or more primers targeting characteristic oncogenicmutations (center). The microdroplets containing the PCR mix may beflowed through a channel that incubates the droplets under conditionseffective for PCR. In the figure, this is achieved by flowing themicrodroplets through a channel that snakes over various zonesmaintained at 65° C. and 95° C. As the microdroplets move through thezones, their temperature cycles, as needed for PCR. During the PCRreaction, if a microdroplet contains a genome of a cell with a mutationfor which the primer(s) are designed to detect, amplification isinitiated. The presence of these particular PCR products may be detectedby, for example, a fluorescent output that turns the microdropletsfluorescent (FIGS. 3-4). The microdroplets may thus be scanned, such asby using flow cytometry, to detect the presence of fluorescent drops(FIG. 14, Panels A-B). In certain aspects, the drops may also be sortedusing, for example, droplet sorting to recover drops of interest(right). Using the nomenclature of the current disclosure, the stepsdescribed above are thus performed “under microfluidic control.” Thatis, the steps are performed on one or more microfluidics devices, or atleast in part on one or more microfluidic devices.

FIG. 2, Panels A-E depict a microfluidics system involving many of thegeneral principles and steps described above. Here, yeast cells (blackspecks) enter from the far left and are encapsulated into drops, shownat low (4× objective; Panel A) and high magnification (10× objective;Panel B). The drops are incubated to allow the yeast to produce asecreted product (Panel C); this produces a fluorescent compound in thedrops, so that drops containing efficient producers quickly becomefluorescent (Panel D). The drops are then sorted to extract the mostefficient yeast using a microfluidic sorter (Panel E).

Encapsulating a component from a biological sample may be achieved byany convenient means. FIG. 5 presents but one possible example, in whichdroplets are formed in a massively parallel fashion a serial bisectiondevice. For instance, cell-containing solution may be injected from theleft and formed into large drops, which flow into the serial bisectionarray and are split into small drops; drops shown to the far right are25 mm in diameter. Encapsulation approaches of interest also include,but are not limited to, hydrodynamically-triggered drop formation andthose described by Link, et al., Phys. Rev. Lett. 92, 054503 (2004), thedisclosure of which is incorporated herein by reference.

As evidenced by FIGS. 1, 4, and 6, a feature of certain methods of thepresent disclosure is the use of a polymerase chain reaction (PCR)-basedassay to detect the presence of certain oligonucleotides and/oroncogene(s) present in cells. Examples of PCR-based assays of interestinclude, but are not limited to, quantitative PCR (qPCR), quantitativefluorescent PCR (QF-PCR), multiplex fluorescent PCR (MF-PCR), singlecell PCR, PCR-RFLP/real time-PCR-RFLP, hot start PCR, nested PCR, insitu polony PCR, in situ rolling circle amplification (RCA), bridge PCR,picotiter PCR, emulsion PCR and reverse transcriptase PCR (RT-PCR).Other suitable amplification methods include the ligase chain reaction(LCR), transcription amplification, self-sustained sequence replication,selective amplification of target polynucleotide sequences, consensussequence primed polymerase chain reaction (CP-PCR), arbitrarily primedpolymerase chain reaction (AP-PCR), degenerate oligonucleotide-primedPCR (DOP-PCR) and nucleic acid based sequence amplification (NABSA).

A PCR-based assay may be used to detect the presence of certain gene(s),such as certain oncogene(s). FIG. 4, Panels A-B depict a PCR-based assayto detect oncogenes. In this assay, one or more primers specific to eachoncogene of interest are reacted with the genome of each cell. Theseprimers have sequences specific to the particular oncogene, so that theywill only hybridize and initiate PCR when they are complimentary to thegenome of the cell. If an oncogene is present and the primer is a match,large many copies of the oncogene are created. To determine whether anoncogene is present, the PCR products may be detected through an assayprobing the liquid of the drop, such as by staining the solution with anintercalating dye, like SybrGreen or ethidium bromide, hybridizing thePCR products to a solid substrate, such as a bead (e.g., magnetic orfluorescent beads, such as Luminex beads), or detecting them through anintermolecular reaction, such as FRET. These dyes, beads, and the likeare each examples of a “detection component,” a term that is usedbroadly and generically herein to refer to any component that is used todetect the presence or absence of PCR product(s).

A great number of variations of these basic approaches will now beoutlined in greater detail below.

Detecting Rare Cells (e.g., Tumor Cells)

Aspects of the subject methods involve detecting the presence of one ormore subset of cells (e.g., tumor cells) in a biological sample. Anexample of such a scheme is depicted in FIG. 6. To use this approach forthe detection of, e.g., tumor cells, a biological sample (e.g., wholeblood) may be recovered from a subject using any convenient means. Thebiological sample may be processed to remove components other than cellsusing, for example, processing steps such as centrifugation, filtration,and the like.

Each cell in the biological sample is then encapsulated into amicrodroplet using a microfluidic device, such as that shown in FIGS. 5and/or 8. Using the example from FIG. 5, the cell-containing solution isinjected from the left and formed into large drops, which flow into theserial bisection array and are split into smaller droplets. Othermethods of encapsulating cells into droplets are known in the art. Wheredesired, the cells may be stained with one or more antibodies and/orprobes prior to encapsulating them into microdroplets. As used herein,the terms “drop,” “droplet,” and “microdroplet” may be usedinterchangeably to refer to tiny, generally spherical, microcompartmentscontaining at least a first fluid phase, e.g., an aqueous phase (e.g.,water), bounded by a second fluid phase (e.g., oil) which is immisciblewith the first fluid phase. In some embodiments, the second fluid phasewill be an immiscible phase carrier fluid. Microdroplets generally rangefrom 0.1 to 1000 μm in diameter, and may be used to encapsulate cells,DNA, enzymes, and other components. Accordingly, the above terms may beused to refer to a droplet produced in, on, or by a microfluidicsdevice.

One or more lysing agents may also be added to the microdropletscontaining a cell, under conditions in which the cell(s) may be causedto burst, thereby releasing their genomes. The lysing agents may beadded after the cells are encapsulated into microdroplets. Anyconvenient lysing agent may be employed, such as proteinase K orcytotoxins. In particular embodiments, cells may be co-encapsulated inmicrodroplets with lysis buffer containing detergents such as TritonX100 and/or proteinase K. The specific conditions in which the cell(s)may be caused to burst will vary depending on the specific lysing agentused. For example, if proteinase K is incorporated as a lysing agent,the microdroplets may be heated to about 37-60° C. for about 20 min tolyse the cells and to allow the proteinase K to digest cellularproteins, after which they may be heated to about 95° C. for about 5-10min to deactivate the proteinase K.

In certain aspects, cell lysis may also, or instead, rely on techniquesthat do not involve addition of lysing agent. For example, lysis may beachieved by mechanical techniques that may employ various geometricfeatures to effect piercing, shearing, abrading, etc. of cells. Othertypes of mechanical breakage such as acoustic techniques may also beused. Further, thermal energy can also be used to lyse cells. Anyconvenient means of effecting cell lysis may be employed in the methodsdescribed herein.

Primers may be introduced into the microdroplet for each of the genesand/or genetic markers, e.g., oncogenes, to be detected. Hence, incertain aspects, primers for a variety of genes and/or genetic markers,e.g., all oncogenes may be present in the microdroplet at the same time,thereby providing a multiplexed assay. The microdroplets aretemperature-cycled so that microdroplets containing cancerous cells, forexample, will undergo PCR. During this time, only the primerscorresponding to oncogenes and/or genetic markers present in the genomewill induce amplification, creating many copies of these oncogenesand/or genetic markers in the microdroplet. Detecting the presence ofthese PCR products may be achieved by a variety of ways, such as byusing FRET, staining with an intercalating dye, or attaching them to abead. For more information on the different options for this, see thesection describing variations of the technique. The microdroplet may beoptically probed to detect the PCR products (FIG. 14). Optically probingthe microdroplet may involve counting the number of tumor cells presentin the initial population, and/or allowing for the identification of theoncogenes present in each tumor cell.

The subject methods may be used to determine whether a biological samplecontains particular cells of interest, e.g., tumor cells, or not. Incertain aspects, the subject methods may include quantifying the numberof cells of interest, e.g., tumor cells, present in a biological sample.Quantifying the number of cells of interest, e.g., tumor cells, presentin a biological sample may be based at least in part on the number ofmicrodroplets in which PCR amplification products were detected. Forexample, microdroplets may be produced under conditions in which themajority of microdroplets are expected to contain zero or one cell.Those microdroplets that do not contain any cells may be removed, usingtechniques described more fully herein. After performing the PCR stepsoutlined above, the total number of microdroplets that are detected tocontain PCR products may be counted, so as to quantify the number ofcells of interest, e.g., tumor cells, in the biological sample. Incertain aspects, the methods may also include counting the total numberof microdroplets so as to determine the fraction or percentage of cellsfrom the biological sample that are cells of interest, e.g., tumorcells.

PCR-Activated Virus Sorting (PAVS)

In some embodiments, referred to herein as PCR-Activated Virus Sorting(PAVS), a biological sample including viruses is encapsulated inmicrodroplets and subjected to PCR conditions, e.g., droplet PCR. Theviruses may be encapsulated in microdroplets using any of the suitablemethods and/or devices described herein or known in the art. Wheredesired, the viruses may be detectably labeled prior to encapsulatingthem into microdroplets.

One or more lysing agents may also be added to the microdropletscontaining virus, under conditions in which the virus(es) may be lysed,thereby releasing their genomes. The lysing agents may be added afterthe viruses are encapsulated into microdroplets. Any convenient lysingagent may be employed, such as proteinase K or guanidine thiocyanate,provided that it is compatible with the microdroplet structure. Inparticular embodiments, viruses may be co-encapsulated in microdropletswith lysis buffer containing detergents such as Triton X100 and/orproteinase K. The specific conditions in which the viruses may be causedto release their genomic material will vary depending on the specificlysing agent used.

In certain aspects, lysis of virus particles may also, or instead, relyon techniques that do not involve the addition of a lysing agent. Forexample, suitable thermal lysis techniques may be utilized. Anyconvenient means of effecting lysis of viral particles may be employedin the methods described herein.

Primers may be introduced into the microdroplets for each of the viralnucleic acids to be detected. The microdroplets are thentemperature-cycled so that microdroplets containing the target viralnucleic acids will undergo PCR. During this time, only the primerscorresponding to the target viral nucleic acids will induceamplification, creating many copies of these nucleic acids in themicrodroplet. Detecting the presence of these PCR products may beachieved in a variety of ways, such as by using FRET, staining with anintercalating dye, or attaching them to a bead. For more information onthe different options for this, see the section describing variations ofthe technique. The microdroplet may be optically probed to detect thePCR products.

The subject methods may be used to determine whether a biological samplecontains particular viruses of interest, or not. In certain aspects, thesubject methods may include quantifying the number of viruses ofinterest present in a biological sample. Quantifying the number ofviruses of interest present in a biological sample may be based at leastin part on the number of microdroplets in which PCR amplificationproducts were detected. For example, microdroplets may be produced underconditions in which the majority of microdroplets are expected tocontain zero or one virus. Those microdroplets that do not contain anyviruses may be removed, using techniques described more fully herein.After performing the PCR steps outlined above, the total number ofmicrodroplets that are detected to contain PCR products may be counted,so as to quantify the number of viruses of interest in the biologicalsample. In certain aspects, the methods may also include counting thetotal number of microdroplets so as to determine the fraction orpercentage of viruses from the biological sample that are viruses ofinterest.

The viruses of interest are then recovered by sorting the microdropletsand recovering their contents via microdroplet rupture, e.g., throughchemical, electrical, or mechanical means as described in greater detailherein. A variety of suitable sorting techniques and related devices maybe utilized sort and separate the microdroplets containing PCRamplification products including those described herein.

PCR-Activated Cell Sorting (PACS)

In some embodiments, referred to herein as PCR-Activated Cell Sorting(PACS), a biological sample including cells is encapsulated inmicrodroplets and subjected to PCR conditions, e.g., droplet PCR. Thecells may be encapsulated in microdroplets using any of the suitablemethods and/or devices described herein or known in the art. Wheredesired, the cells may be detectably labeled, e.g., with one or moreantibodies and/or probes, prior to encapsulating them intomicrodroplets.

One or more lysing agents may also be added to the microdropletscontaining a cell, under conditions in which the cell(s) may be lysed,thereby releasing their genomes. The lysing agents may be added afterthe cells are encapsulated into microdroplets. Any convenient lysingagent may be employed, such as proteinase K or cytotoxis, provided thatit is compatible with the microdroplet structure. In particularembodiments, cells may be co-encapsulated in microdroplets with lysisbuffer containing detergents such as Triton X100 and/or proteinase K.The specific conditions in which the cell(s) may be caused to releasetheir genomic material will vary depending on the specific lysing agentused. For example, if proteinase K is incorporated as a lysing agent,the microdroplets may be heated to about 37-60° C. for about 20 min tolyse the cells and to allow the proteinase K to digest cellularproteins, after which they may be heated to about 95° C. for about 5-10min to deactivate the proteinase K.

In certain aspects, cell lysis may also, or instead, rely on techniquesthat do not involve the addition of a lysing agent. For example, lysismay be achieved by mechanical techniques that may employ variousgeometric features to effect piercing, shearing, abrading, etc. ofcells. Other types of mechanical breakage such as acoustic techniquesmay also be used. Further, thermal energy can also be used to lysecells. Any convenient means of effecting cell lysis may be employed inthe methods described herein.

Primers may be introduced into the microdroplets for each of the nucleicacids to be detected for a cell of interest. The microdroplets are thentemperature-cycled so that microdroplets containing the target nucleicacids for the target cells will undergo PCR. During this time, only theprimers corresponding to the target cellular nucleic acids will induceamplification, creating many copies of these nucleic acids in themicrodroplet. Detecting the presence of these PCR products may beachieved in a variety of ways, such as by using FRET, staining with anintercalating dye, or attaching them to a bead. For more information onthe different options for this, see the section describing variations ofthe technique. The microdroplet may be optically probed to detect thePCR products.

The subject methods may be used to determine whether a biological samplecontains particular cells of interest, or not. In certain aspects, thesubject methods may include quantifying the number of cells of interestpresent in a biological sample. Quantifying the number of cells ofinterest present in a biological sample may be based at least in part onthe number of microdroplets in which PCR amplification products weredetected. For example, microdroplets may be produced under conditions inwhich the majority of microdroplets are expected to contain zero or onecell. Those microdroplets that do not contain any cells may be removed,using techniques described more fully herein. After performing the PCRsteps outlined above, the total number of microdroplets that aredetected to contain PCR products may be counted, so as to quantify thenumber of cells of interest in the biological sample. In certainaspects, the methods may also include counting the total number ofmicrodroplets so as to determine the fraction or percentage of cellsfrom the biological sample that are cells of interest.

The cells and/or cellular material of interest are then recovered bysorting the microdroplets and recovering their contents via microdropletrupture, e.g., through chemical, electrical, or mechanical means asdescribed in greater detail herein. A variety of suitable sortingtechniques and related devices may be utilized sort and separate themicrodroplets containing PCR amplification products including thosedescribed herein.

PACS may be utilized, e.g., for the cultivation-free enrichment andsequencing of rare microbes and/or cells, e.g., as described in greaterdetail in Example 11.

PCR-Activated Nucleic Acid Sorting (PANS)

In some embodiments, referred to herein as PCR-Activated Nucleic AcidSorting (PANS), a sample including nucleic acids (e.g., DNA and/or RNA)is encapsulated in microdroplets and subjected to PCR conditions, e.g.,RT-PCR conditions, PCR (or RT-PCR). PCR, e.g., RT-PCR, assays specificto the nucleic acids of interest cause microdroplets containing thenucleic acids of interest to become detectably labeled, e.g.,fluorescently labeled. The nucleic acids of interest are then recoveredby sorting the microdroplets and recovering their contents viamicrodroplet rupture, e.g., through chemical or electrical means.

In one aspect of PANS, a method for enriching for a target nucleic acidsequence is provided, wherein the method includes encapsulating a sampleincluding nucleic acids in a plurality of microdroplets, eachmicrodroplet including a first aqueous phase fluid in an immisciblephase carrier fluid; introducing polymerase chain reaction (PCR)reagents and a plurality of PCR primers into the microdroplets;incubating the microdroplets under conditions sufficient for PCRamplification to produce PCR amplification products, wherein theplurality of PCR primers include one or more primers that each hybridizeto one or more oligonucleotides comprised by the target nucleic acidsequence, and wherein the PCR amplification products do not include theentire target nucleic acid sequence; introducing a detection componentinto the microdroplets either before or after the incubating; detectingthe presence or absence of the PCR amplification products by detectionof the detection component, wherein detection of the detection componentindicates the presence of PCR amplification products and the targetnucleic acid sequence; and sorting the microdroplets based on detectionof the detection component, wherein the sorting separates microdropletsincluding the PCR amplification products and the target nucleic acidsequence, when present, from microdroplets which do not include the PCRamplification products and the target nucleic acid sequence; and poolingthe nucleic acid sequences from the sorted microdroplets to provide anenriched pool of target nucleic acid sequences, when present. One ormore of these steps may be performed under microfluidic control.

The above method allows, for example, for the enrichment of DNAmolecules out of a heterogeneous system based on the presence ofPCR-detectable subsequences. The DNA molecules can be short (e.g.,hundreds of bases) or long (e.g., megabases or longer). The sample maybe encapsulated in microdroplets such that target molecules are detectedin the microdroplets digitally—i.e., each microdroplet contains 0 or 1target molecule. The microdroplets may then be sorted based on, e.g.,fluorescence, to recover the target molecules. This method can be usedto enrich for a large genomic region, e.g., on the order of megabases inlength, in a heterogeneous sample of DNA fragments.

The above method enables a sufficient amount of DNA to be recoveredwithout the need to perform PCR to amplify the DNA for sequencing.Amplification-free DNA sample prep is valuable, for example, where PCRdoes not preserve the sequences or epigenetic factors of interest, orcannot recover sequences that are of the needed length (e.g., >about 10kb, the practical limit of long-range PCR).

Another application is to apply PANS to enrich DNA for epigeneticsequencing. Epigenetic marks on DNA are not preserved by PCR, sosequencing them requires unamplified DNA from the host nucleic acids.With PANS, a sufficient amount of DNA can be obtained for sequencingwithout needing to perform PCR, and thus preserving the epigeneticmarks.

An embodiment of the PANS method is depicted generally in FIG. 71.Briefly, megabase size fragments of genomic DNA may be encapsulated intomicrodroplets, e.g., along with suitable PCR reagents, including, e.g.,PCR primers which hybridize to one or more oligonucleotides including atarget nucleic acid sequence. The microdroplets may then be thermocycled(either on-chip or off) to produce PCR amplification products whichidentify, e.g., via a detectable label, microdroplets which contain thetarget nucleic acid sequences, but which do not contain amplicons of thecomplete target nucleic acid sequence. Microdroplets which contain thetarget nucleic acid sequences may then be sorted using any suitablemethod, e.g., dielectrophoresis or flow cytometry, and separated frommicrodroplets which do not include the target nucleic acid sequences,thereby enriching for the target nucleic acid sequences without directlyamplifying the complete target nucleic acid sequences. The enrichedtarget nucleic acid may then be purified and sequenced as desired usingany suitable method. As discussed above, this embodiment of the PANSmethod has particular utility where the length of the target nucleicacid exceeds the practical limits of long-range PCR, e.g., where thenucleic acid is greater than about 10 kb, and/or where it is desirableto preserve epigenetic marks on the DNA. In some embodiments, the targetnucleic acid to be enriched is greater than about 100 kb in length,e.g., greater than about 1 megabase in length. In some embodiments, thetarget nucleic acid to be enriched is from about 10 kb to about 100 kb,from about 100 kb to about 500 kb, or from about 500 kb to about 1megabase in length.

PCR

As summarized above, in practicing methods of the invention a PCR-basedassay may be used to detect the presence of certain genes of interestand/or genetic markers, e.g., oncogene(s), present in cells or aheterogeneous sample of nucleic acids. The conditions of such PCR-basedassays may vary in one or more ways.

For instance, the number of PCR primers that may be added to amicrodroplet may vary. The term “primer” may refer to more than oneprimer and refers to an oligonucleotide, whether occurring naturally, asin a purified restriction digest, or produced synthetically, which iscapable of acting as a point of initiation of synthesis along acomplementary strand when placed under conditions in which synthesis ofa primer extension product which is complementary to a nucleic acidstrand is catalyzed. Such conditions include the presence of fourdifferent deoxyribonucleoside triphosphates and apolymerization-inducing agent such as DNA polymerase or reversetranscriptase, in a suitable buffer (“buffer” includes substituentswhich are cofactors, or which affect pH, ionic strength, etc.), and at asuitable temperature. The primer is preferably single-stranded formaximum efficiency in amplification.

The complement of a nucleic acid sequence as used herein refers to anoligonucleotide which, when aligned with the nucleic acid sequence suchthat the 5′ end of one sequence is paired with the 3′ end of the other,is in “antiparallel association.” Complementarity need not be perfect;stable duplexes may contain mismatched base pairs or unmatched bases.Those skilled in the art of nucleic acid technology can determine duplexstability empirically considering a number of variables including, forexample, the length of the oligonucleotide, percent concentration ofcytosine and guanine bases in the oligonucleotide, ionic strength, andincidence of mismatched base pairs.

The number of PCR primers that may be added to a microdroplet may rangefrom about 1 to about 500 or more, e.g., about 2 to 100 primers, about 2to 10 primers, about 10 to 20 primers, about 20 to 30 primers, about 30to 40 primers, about 40 to 50 primers, about 50 to 60 primers, about 60to 70 primers, about 70 to 80 primers, about 80 to 90 primers, about 90to 100 primers, about 100 to 150 primers, about 150 to 200 primers,about 200 to 250 primers, about 250 to 300 primers, about 300 to 350primers, about 350 to 400 primers, about 400 to 450 primers, about 450to 500 primers, or about 500 primers or more.

These primers may contain primers for one or more gene of interest, e.g.oncogenes. The number of primers for genes of interest that are addedmay be from about one to 500, e.g., about 1 to 10 primers, about 10 to20 primers, about 20 to 30 primers, about 30 to 40 primers, about 40 to50 primers, about 50 to 60 primers, about 60 to 70 primers, about 70 to80 primers, about 80 to 90 primers, about 90 to 100 primers, about 100to 150 primers, about 150 to 200 primers, about 200 to 250 primers,about 250 to 300 primers, about 300 to 350 primers, about 350 to 400primers, about 400 to 450 primers, about 450 to 500 primers, or about500 primers or more. Genes and oncogenes of interest include, but arenot limited to, BAX, BCL2L1, CASP8, CDK4, ELK1, ETS1, HGF, JAK2, JUNB,JUND, KIT, KITLG, MCL1, MET, MOS, MYB, NFKBIA, EGFR, Myc, EpCAM, NRAS,PIK3CA, PML, PRKCA, RAF1, RARA, REL, ROS1, RUNX1, SRC, STAT3, CD45,cytokeratins, CEA, CD133, HER2, CD44, CD49f, CD146, MUC1/2, and ZHX2.

Such primers and/or reagents may be added to a microdroplet in one step,or in more than one step. For instance, the primers may be added in twoor more steps, three or more steps, four or more steps, or five or moresteps. Regardless of whether the primers are added in one step or inmore than one step, they may be added after the addition of a lysingagent, prior to the addition of a lysing agent, or concomitantly withthe addition of a lysing agent. When added before or after the additionof a lysing agent, the PCR primers may be added in a separate step fromthe addition of a lysing agent.

Once primers have been added to a microdroplet the microdroplet may beincubated under conditions allowing for PCR. The microdroplet may beincubated on the same microfluidic device as was used to add theprimer(s), or may be incubated on a separate device. In certainembodiments, incubating the microdroplet under conditions allowing forPCR amplification is performed on the same microfluidic device used toencapsulate the cells and lyse the cells. Incubating the microdropletsmay take a variety of forms. In certain aspects, the drops containingthe PCR mix may be flowed through a channel that incubates themicrodroplets under conditions effective for PCR. Flowing themicrodroplets through a channel may involve a channel that snakes overvarious temperature zones maintained at temperatures effective for PCR.Such channels may, for example, cycle over two or more temperaturezones, wherein at least one zone is maintained at about 65° C. and atleast one zone is maintained at about 95° C. As the drops move throughsuch zones, their temperature cycles, as needed for PCR. The precisenumber of zones, and the respective temperature of each zone, may bereadily determined by those of skill in the art to achieve the desiredPCR amplification.

In other embodiments, incubating the microdroplets may involve the useof a device of the general types depicted in FIG. 12, Panels A-C, andFIG. 13; a device of this general type may be referred to herein as a“Megadroplet Array.” In such a device, an array of hundreds, thousands,or millions of traps indented into a channel (e.g., a PDMS channel) sitabove a thermal system (FIG. 12, Panel A). The channel may bepressurized, thereby preventing gas from escaping. The height of themicrofluidic channel is smaller than the diameter of the drops, causingdrops to adopt a flattened pancake shape. When a drop flows over anunoccupied indentation, it adopts a lower, more energetically favorable,radius of curvature, leading to a force that pulls the drop entirelyinto the trap (FIG. 12, Panel B). By flowing drops as a close pack, itis ensured that all traps on the array are occupied, as illustrated inFIG. 12, Panel C. The entire device may be thermal cycled using aheater.

In certain aspects, the heater includes a Peltier plate, heat sink, andcontrol computer. The Peltier plate allows for the heating or cooling ofthe chip above or below room temperature by controlling the appliedcurrent. To ensure controlled and reproducible temperature, a computermay monitor the temperature of the array using integrated temperatureprobes, and may adjust the applied current to heat and cool as needed. Ametallic (e.g. copper) plate allows for uniform application of heat anddissipation of excess heat during cooling cycles, enabling cooling fromabout 95° C. to about 60° C. in under about one minute.

Methods of the invention may also include introducing one or more probesto the microdroplet. As used herein with respect to nucleic acids, theterm “probe” refers to a labeled oligonucleotide which forms a duplexstructure with a sequence in the target nucleic acid, due tocomplementarity of at least one sequence in the probe with a sequence inthe target region. In some embodiments, the probe does not contain asequence complementary to sequence(s) used to prime the polymerase chainreaction. The number of probes that are added may be from about one to500, e.g., about 1 to 10 probes, about 10 to 20 probes, about 20 to 30probes, about 30 to 40 probes, about 40 to 50 probes, about 50 to 60probes, about 60 to 70 probes, about 70 to 80 probes, about 80 to 90probes, about 90 to 100 probes, about 100 to 150 probes, about 150 to200 probes, about 200 to 250 probes, about 250 to 300 probes, about 300to 350 probes, about 350 to 400 probes, about 400 to 450 probes, about450 to 500 probes, or about 500 probes or more. The probe(s) may beintroduced into the microdroplet prior to, subsequent with, or after theaddition of the one or more primer(s). Probes of interest include, butare not limited to, TaqMan® probes (e.g., as described in Holland, P.M.; Abramson, R. D.; Watson, R.; Gelfand, D. H. (1991). “Detection ofspecific polymerase chain reaction product by utilizing the 5′---3′exonuclease activity of Thermus aquaticus DNA polymerase”. PNAS, 88(16): 7276-7280).

In certain embodiments, an RT-PCR based assay may be used to detect thepresence of certain transcripts of interest, e.g., oncogene(s), presentin cells. In such embodiments, reverse transcriptase and any otherreagents necessary for cDNA synthesis are added to the microdroplet inaddition to the reagents used to carry out PCR described herein(collectively referred to as the “RT-PCR reagents”). The RT-PCR reagentsare added to the microdroplet using any of the methods described herein.Once reagents for RT-PCR have been added to a microdroplet, themicrodroplet may be incubated under conditions allowing for reversetranscription followed by conditions allowing for PCR as describedherein. The microdroplet may be incubated on the same microfluidicdevice as was used to add the RT-PCR reagents, or may be incubated on aseparate device. In certain embodiments, incubating the microdropletunder conditions allowing for RT-PCR is performed on the samemicrofluidic device used to encapsulate the cells and lyse the cells.

In certain embodiments, the reagents added to the microdroplet forRT-PCR or PCR further includes a fluorescent DNA probe capable ofdetecting RT-PCR or PCR products. Any suitable fluorescent DNA probe canbe used including, but not limited to SYBR Green, TaqMan®, MolecularBeacons and Scorpion probes. In certain embodiments, the reagents addedto the microdroplet include more than one DNA probe, e.g., twofluorescent DNA probes, three fluorescent DNA probes, or fourfluorescent DNA probes. The use of multiple fluorescent DNA probesallows for the concurrent measurement of RT-PCR or PCR products in asingle reaction.

Double PCR

To amplify rare transcripts, a microdroplet that has undergone afirst-step RT-PCR or PCR reaction as described herein may be furthersubjected to a second step PCR reaction. In some embodiments, a portionof a microdroplet that has undergone a first-step RT-PCR or PCR reactionis extracted from the microdroplet and coalesced with a dropletcontaining additional PCR reagents, including, but not limited toenzymes (e.g. DNA polymerase), DNA probes (e.g. fluorescent DNA probes)and primers. In certain embodiments, the droplet containing theadditional PCR reagents is larger than the microdroplet that hasundergone the first step RT-PCR or PCR reaction. This may be beneficial,for example, because it allows for the dilution of cellular componentsthat may be inhibitory to the second step PCR. The second step PCRreaction may be carried out on the same microfluidic device used tocarry out the first-step reaction or on a different microfluidic device.

In some embodiments, the primers used in the second step PCR reactionare the same primers used in the first step RT-PCR or PCR reaction. Inother embodiments, the primers used in the second step PCR reaction aredifferent than the primers used in the first step reaction.

Multiplexing

In certain embodiments of the subject methods, multiple biomarkers maybe detected and analyzed for a particular cell. Biomarkers detected mayinclude, but are not limited to, one or more proteins, transcriptsand/or genetic signatures in the cell's genome or combinations thereof.With standard fluorescence based detection, the number of biomarkersthat can be simultaneously interrogated may be limited to the number offluorescent dyes that can be independently visualized within eachmicrodrop. In certain embodiments, the number of biomarkers that can beindividually detected within a particular microdroplet can be increased.For example, this may be accomplished by segregation of dyes todifferent parts of the microdroplet. In particular embodiments, beads(e.g. LUMINEX® beads) conjugated with dyes and probes (e.g., nucleicacid or antibody probes) may be encapsulated in the microdroplet toincrease the number of biomarkers analyzed. In another embodiment,fluorescence polarization may be used to achieve a greater number ofdetectable signals for different biomarkers for a single cell. Forexample, fluorescent dyes may be attached to various probes and themicrodroplet may be visualized under different polarization conditions.In this way, the same colored dye can be utilized to provide a signalfor different probe targets for a single cell. The use of fixed and/orpermeabilized cells (as discussed in greater detail below) also allowsfor increased levels of multiplexing. For example, labeled antibodiesmay be used to target protein targets localized to cellular componentswhile labeled PCR and/or RT-PCR products are free within a microdroplet.This allows for dyes of the same color to be used for antibodies and foramplicons produced by RT-PCR.

Types of Microdroplets

In practicing the methods of the present invention, the composition andnature of the microdroplets may vary. For instance, in certain aspects,a surfactant may be used to stabilize the microdroplets. Accordingly, amicrodroplet may involve a surfactant stabilized emulsion. Anyconvenient surfactant that allows for the desired reactions to beperformed in the drops may be used. In other aspects, a microdroplet isnot stabilized by surfactants or particles.

The surfactant used depends on a number of factors such as the oil andaqueous phases (or other suitable immiscible phases, e.g., any suitablehydrophobic and hydrophilic phases) used for the emulsions. For example,when using aqueous droplets in a fluorocarbon oil, the surfactant mayhave a hydrophilic block (PEG-PPO) and a hydrophobic fluorinated block(Krytox FSH). If, however, the oil was switched to be a hydrocarbon oil,for example, the surfactant would instead be chosen so that it had ahydrophobic hydrocarbon block, like the surfactant ABIL EM90. Inselecting a surfactant, desirable properties that may be considered inchoosing the surfactant may include one or more of the following: (1)the surfactant has low viscosity; (2) the surfactant is immiscible withthe polymer used to construct the device, and thus it doesn't swell thedevice; (3) biocompatibility; (4) the assay reagents are not soluble inthe surfactant; (5) the surfactant exhibits favorable gas solubility, inthat it allows gases to come in and out; (6) the surfactant has aboiling point higher than the temperature used for PCR (e.g., 95 C); (7)the emulsion stability; (8) that the surfactant stabilizes drops of thedesired size; (9) that the surfactant is soluble in the carrier phaseand not in the droplet phase; (10) that the surfactant has limitedfluorescence properties; and (11) that the surfactant remains soluble inthe carrier phase over a range of temperatures.

Other surfactants can also be envisioned, including ionic surfactants.Other additives can also be included in the oil to stabilize the drops,including polymers that increase droplet stability at temperatures above35° C.

The microdroplets described herein may be prepared as emulsions, e.g.,as an aqueous phase fluid dispersed in an immiscible phase carrier fluid(e.g., a fluorocarbon oil or a hydrocarbon oil) or vice versa. In someembodiments, where a particular sorting technique benefits from orrequires that the microdroplets be provided in an aqueous phase fluid,e.g., in the case of sorting via FACS, the microdroplets may be providedas double-emulsions following a nucleic acid amplification step, e.g.,as an aqueous phase fluid in an immiscible phase fluid, dispersed in anaqueous phase carrier fluid; quadruple emulsions, e.g., an aqueous phasefluid in an immiscible phase fluid, in an aqueous phase fluid, in animmiscible phase fluid, dispersed in an aqueous phase carrier fluid; andso on. The nature of the microfluidic channel (or a coating thereon),e.g., hydrophilic or hydrophobic, may be selected so as to be compatiblewith the type of emulsion being utilized at a particular point in amicrofluidic work flow. See, e.g., FIG. 23 in which a hydrophilicchannel is utilized in connection with a double emulsion stage whereas ahydrophobic channel is utilized in connection with a triple emulsionstage.

Adding Reagents to Microdroplets

In practicing the subject methods, a number of reagents may need to beadded to the microdroplets, in one or more steps (e.g., about 2, about3, about 4, or about 5 or more steps). The means of adding reagents tothe microdroplets may vary in a number of ways. Approaches of interestinclude, but are not limited to, those described by Ahn, et al., Appl.Phys. Lett. 88, 264105 (2006); Priest, et al., Appl. Phys. Lett. 89,134101 (2006); Abate, et al., PNAS, Nov. 9, 2010 vol. 107 no. 4519163-19166; and Song, et al., Anal. Chem., 2006, 78 (14), pp 4839-4849;the disclosures of which are incorporated herein by reference.

For instance, a reagent may be added to a microdroplet, e.g., a droplet,by a method involving merging a microdroplet with a second microdropletthat contains the reagent(s). The reagent(s) that are contained in thesecond microdroplet may be added by any convenient means, specificallyincluding those described herein. This microdroplet may be merged withthe first microdroplet to create a microdroplet that includes thecontents of both the first microdroplet and the second microdroplet.

One or more reagents may also, or instead, be added using techniquessuch as droplet coalescence, or picoinjection. In droplet coalescence, atarget microdroplet may be flowed alongside a microdroplet containingthe reagent(s) to be added to the target microdroplet. The twomicrodroplets may be flowed such that they are in contact with eachother, but not touching other microdroplets. These microdroplets maythen be passed through electrodes or other means of applying anelectrical field, wherein the electric field may destabilize themicrodroplets such that they are merged together.

Reagents may also, or instead, be added using picoinjection. In thisapproach, a target microdroplet may be flowed past a channel containingthe reagent(s) to be added, wherein the reagent(s) are at an elevatedpressure. Due to the presence of the surfactants, however, in theabsence of an electric field, the microdroplet will flow past withoutbeing injected, because surfactants coating the microdroplet may preventthe fluid(s) from entering. However, if an electric field is applied tothe microdroplet as it passes the injector, fluid containing thereagent(s) will be injected into the microdroplet. The amount of reagentadded to the microdroplet may be controlled by several differentparameters, such as by adjusting the injection pressure and the velocityof the flowing drops, by switching the electric field on and off, andthe like.

In other aspects, one or more reagents may also, or instead, be added toa microdroplet by a method that does not rely on merging twomicrodroplets together or on injecting liquid into a microdroplet.Rather, one or more reagents may be added to a microdroplet by a methodinvolving the steps of emulsifying a reagent into a stream of very smalldrops, and merging these small drops with a target microdroplet (FIG.20, Panels A-B). Such methods shall be referred to herein as “reagentaddition through multiple-drop coalescence.” These methods takeadvantage of the fact that due to the small size of the drops to beadded compared to that of the target microdroplet, the small drops willflow faster than the target microdroplets and collect behind them. Thecollection can then be merged by, for example, applying an electricfield. This approach can also, or instead, be used to add multiplereagents to a microdroplet by using several co-flowing streams of smalldrops of different fluids. To enable effective merger of the tiny andtarget microdroplets, it is important to make the tiny drops smallerthan the channel containing the target microdroplets, and also to makethe distance between the channel injecting the target microdroplets fromthe electrodes applying the electric field sufficiently long so as togive the tiny drops time to “catch up” to the target microdroplets. Ifthis channel is too short, not all tiny drops will merge with the targetmicrodroplet and less than the desired amount of reagent may be added.To a certain degree, this can be compensated for by increasing themagnitude of the electric field, which tends to allow drops that arefarther apart to merge. In addition to making the tiny drops on the samemicrofluidic device, as is shown in FIG. 20, Panels A-B, they can also,or instead, be made offline using another microfluidic drop maker orthrough homogenization and then injecting them into the devicecontaining the target microdroplets.

Accordingly, in certain aspects a reagent is added to a microdroplet bya method involving emulsifying the reagent into a stream of droplets,wherein the droplets are smaller than the size of the microdroplet;flowing the droplets together with the microdroplet; and merging adroplet with the microdroplet. The diameter of the droplets contained inthe stream of droplets may vary ranging from about 75% or less than thatof the diameter of the microdroplet, e.g., the diameter of the flowingdroplets is about 75% or less than that of the diameter of themicrodroplet, about 50% or less than that of the diameter of themicrodroplet, about 25% or less than that of the diameter of themicrodroplet, about 15% or less than that of the diameter of themicrodroplet, about 10% or less than that of the diameter of themicrodroplet, about 5% or less than that of the diameter of themicrodroplet, or about 2% or less than that of the diameter of themicrodroplet. In certain aspects, a plurality of flowing droplets may bemerged with the microdroplet, such as 2 or more droplets, 3 or more, 4or more, or 5 or more. Such merging may be achieved by any convenientmeans, including but not limited to by applying an electric field,wherein the electric field is effective to merge the flowing dropletwith the microdroplet.

As a variation of the above-described methods, the fluids may bejetting. That is, rather than emulsifying the fluid to be added intoflowing droplets, a long jet of this fluid can be formed and flowedalongside the target microdroplet. These two fluids can then be mergedby, for example, applying an electric field. The result is a jet withbulges where the microdroplets are, which may naturally break apart intodroplets of roughly the size of the target microdroplets before themerger, due to the Rayleigh plateau instability. A number of variantsare contemplated. For instance, one or more agents may be added to thejetting fluid to make it easier to jet, such as gelling agents and/orsurfactants. Moreover, the viscosity of the continuous fluid could alsobe adjusted to enable jetting, such as that described by Utada, et al.,Phys. Rev. Lett. 99, 094502 (2007), the disclosure of which isincorporated herein by reference.

In other aspects, one or more reagents may be added using a method thatuses the injection fluid itself as an electrode, by exploiting dissolvedelectrolytes in solution (FIGS. 15-19). Methods of this general type aredescribed more fully herein in Example 3.

In another aspect, a reagent is added to a microdroplet formed at anearlier time by enveloping the microdroplet to which the reagent is tobe added (i.e., the “target microdroplet”) inside a drop containing thereagent to be added (the “target reagent”). In certain embodiments sucha method is carried out by first encapsulating the target microdropletin a shell of a suitable hydrophobic phase, e.g., oil, to form a doubleemulsion. The double emulsion is then encapsulated by a microdropletcontaining the target reagent to form a triple emulsion. To combine thetarget drop with the drop containing the target reagent, the doubleemulsion is then burst open using any suitable method, including, butnot limited to, applying an electric field, adding chemicals thatdestabilizes the microdroplet interface, flowing the triple emulsionthrough constrictions and other microfluidic geometries, applyingmechanical agitation or ultrasound, increasing or reducing temperature,or by encapsulating magnetic particles in the microdroplet that canrupture the double emulsion interface when pulled by a magnetic field.Methods of making a triple emulsion and combining a target drop with atarget reagent are described in Example 4 provided herein.

Detecting PCR Products

In practicing the subject methods, the manner in which PCR products maybe detected may vary. For example, if the goal is simply to count thenumber of a particular cell type, e.g., tumor cells, present in apopulation, this may be achieved by using a simple binary assay in whichSybrGreen, or any other stain and/or intercalating stain, is added toeach microdroplet so that in the event a characterizing gene, e.g., anoncogene, is present and PCR products are produced, the microdropletwill become fluorescent. The change in fluorescence may be due tofluorescence polarization. The detection component may include the useof an intercalating stain (e.g., SybrGreen).

A variety of different detection components may be used in practicingthe subject methods, including using fluorescent dyes known in the art.Fluorescent dyes may typically be divided into families, such asfluorescein and its derivatives; rhodamine and its derivatives; cyanineand its derivatives; coumarin and its derivatives; Cascade Blue and itsderivatives; Lucifer Yellow and its derivatives; BODIPY and itsderivatives; and the like. Exemplary fluorophores includeindocarbocyanine (C3), indodicarbocyanine (C5), Cy3, Cy3.5, Cy5, Cy5.5,Cy7, Texas Red, Pacific Blue, Oregon Green 488, Alexa fluor-355, AlexaFluor 488, Alexa Fluor 532, Alexa Fluor 546, Alexa Fluor-555, AlexaFluor 568, Alexa Fluor 594, Alexa Fluor 647, Alexa Fluor 660, AlexaFluor 680, JOE, Lissamine, Rhodamine Green, BODIPY, fluoresceinisothiocyanate (FITC), carboxy-fluorescein (FAM), phycoerythrin,rhodamine, dichlororhodamine (dRhodamine), carboxy tetramethylrhodamine(TAMRA), carboxy-X-rhodamine (ROX), LIZ, VIC, NED, PET, SYBR, PicoGreen,RiboGreen, and the like. Descriptions of fluorophores and their use, canbe found in, among other places, R. Haugland, Handbook of FluorescentProbes and Research Products, 9th ed. (2002), Molecular Probes, Eugene,Oreg.; M. Schena, Microarray Analysis (2003), John Wiley & Sons,Hoboken, N.J.; Synthetic Medicinal Chemistry 2003/2004 Catalog, Berryand Associates, Ann Arbor, Mich.; G. Hermanson, Bioconjugate Techniques,Academic Press (1996); and Glen Research 2002 Catalog, Sterling, Va.

FIG. 14, Panels A-B depict the use of a one-color flow-cytometer, whichcan be used, for example, to detect tumor cell containing microdroplets.Panel A presents a schematic of a detector, consisting of a 488 nm laserdirected into the back of an objective, and focused onto a microfluidicchannel through which the microdroplets flow. The laser may excitefluorescent dyes within the microdroplets, and any emitted light iscaptured by the objective and imaged onto a PMT after it is filteredthrough a dichroic mirror and 520 f 5 nm band pass filter. Turning toPanel B, microdroplet appear as peaks in intensity as a function oftime, as shown by the output voltage of a PMT, which is proportional tothe intensity of the emitted light, as a function of time for detectedfluorescent microdroplets.

FIGS. 3 and 4, Panels A-B further illustrate such a concept. FIG. 3, forexample, is a non-limiting example that depicts digital detection ofBRAF using TaqMan® PCR assays in arrayed microdroplets. Fluorescentmicrodroplets indicate amplification of the BRAF gene from human genomicDNA, while non-fluorescent microdroplets were devoid of the gene.Turning to FIG. 4, Panels A-B, this scheme is generalized. In FIG. 4,Panel A, a schematic is presented showing forward and reverse primersbeing encapsulated in the microdroplets that target an oncogenicsequence. If the oncogenic sequence is present, the PCR reactionproduces double-stranded PCR products (Panel A, upper), whereas, if itis not, no products are produced (Panel A, lower). SybrGreen, or anyother type of intercalating stain, is also present in the microdroplet.The results are depicted by the images in FIG. 4, Panel B, in that ifdouble-stranded products are produced, the dye intercalates into them,becoming fluorescent, and turning the microdroplet fluorescent (FIG. 4,Panel B, upper); by contrast, if no double-stranded products areproduced, the dye remains non-fluorescent, producing a dim microdroplet(FIG. 4, Panel B, lower).

In other aspects, particularly if a goal is to further characterize theoncogenes present, additional testing may be needed. For instance, inthe case of the multiplex assays described more fully herein (Example2), this may be achieved by having optical outputs that relate which ofthe gene(s) are amplified in the microdroplet. An alternative approachwould be to use a binary output, for example, with an intercalatedstain, to simply determine which microdroplets have any oncogenes. Thesecan then be sorted to recover these microdroplets so that they could beanalyzed in greater detail to determine which oncogenes they contain. Todetermine the oncogenes present in such a microdroplet, microfluidictechniques or nonmicrofluidic techniques could be used. Usingnon-microfluidic techniques, a microdroplet identified as containing anoncogene can be placed into a well on a wellplate where will be dilutedinto a larger volume, releasing all of the PCR products that werecreated during the multiplexed PCR reaction. Samples from this well canthen be transferred into other wells, into each of which would be addedprimers for one of the oncogenes. These wells would then betemperature-cycled to initiate PCR, at which point an intercalatingstain would be added to cause wells that have matching oncogenes andprimers to light up.

In practicing the subject methods, therefore, a component may bedetected based upon, for example, a change in fluorescence. In certainaspects, the change in fluorescence is due to fluorescence resonanceenergy transfer (FRET). In this approach, a special set of primers maybe used in which the 5′ primer has a quencher dye and the 3′ primer hasa fluorescent dye. These dyes can be arranged anywhere on the primers,either on the ends or in the middles. Because the primers arecomplementary, they will exist as duplexes in solution, so that theemission of the fluorescent dye will be quenched by the quencher dye,since they will be in close proximity to one another, causing thesolution to appear dark. After PCR, these primers will be incorporatedinto the long PCR products, and will therefore be far apart from oneanother. This will allow the fluorescent dye to emit light, causing thesolution to become fluorescent. Hence, to detect if a particularoncogene is present, one may measure the intensity of the droplet at thewavelength of the fluorescent dye. To detect if different oncogenes arepresent, this would be done with different colored dyes for thedifferent primers. This would cause the droplet to become fluorescent atall wavelengths corresponding to the primers of the oncogenes present inthe cell.

Sorting

In practicing the methods of the present disclosure, one or more sortingsteps may be employed. Sorting approaches of interest include, by arenot necessarily limited to, approaches that involve the use of membranevalves, bifurcating channels, surface acoustic waves, and/ordielectrophoresis. Sorting approaches of interest further include thosedepicted in FIGS. 2 and 22, Panels A-B, and those described by Agresti,et al., PNAS vol. 107, no 9, 4004-4009; the disclosure of which isincorporated herein by reference. A population may be enriched bysorting, in that a population containing a mix of members having or nothaving a desired property may be enriched by removing those members thatdo not have the desired property, thereby producing an enrichedpopulation having the desired property.

Sorting may be applied before or after any of the steps describedherein. Moreover, two or more sorting steps may be applied to apopulation of microdroplets, e.g., about 2 or more sorting steps, about3 or more, about 4 or more, or about 5 or more, etc. When a plurality ofsorting steps is applied, the steps may be substantially identical ordifferent in one or more ways (e.g., sorting based upon a differentproperty, sorting using a different technique, and the like).

Moreover, microdroplets may be purified prior to, or after, any sortingstep. FIG. 21 presents a schematic of a microfluidic device whereby amicrodroplet may be purified. That is, a majority of the fluid in themicrodroplet is replaced it with a purified solution, without removingany discrete reagents that may be encapsulated in the microdroplet, sucha cells or beads. The microdroplet is first injected with a solution todilute any impurities within it. The diluted microdroplet is then flowedthrough a microfluidic channel on which an electric field is beingapplied using electrodes. Due to the dielectrophoretic forces generatedby the field, as the cells or other discrete reagents pass through thefield they will be displaced in the flow. The microdroplets are thensplit, so that all the objects end up in one microdroplet. Accordingly,the initial microdroplet has been purified, in that the contaminants maybe removed while the presence and/or concentration of discrete reagents,such as beads or cells, that may be encapsulated within the microdropletare maintained in the resulting microdroplet.

Microdroplets may be sorted based on one or more properties. Propertiesof interest include, but are not limited to, the size, viscosity, mass,buoyancy, surface tension, electrical conductivity, charge, magnetism,and/or presence or absence of one or more components. In certainaspects, sorting may be based at least in part upon the presence orabsence of a cell in the microdroplet. In certain aspects, sorting maybe based at least in part based upon the detection of the presence orabsence of PCR amplification products.

Microdroplet sorting may be employed, for example, to removemicrodroplets in which no cells are present. Encapsulation may result inone or more microdroplets, including a majority of the microdroplets, inwhich no cell is present. If such empty microdroplets were left in thesystem, they would be processed as any other microdroplet, during whichreagents and time would be wasted. To achieve the highest speed andefficiency, these empty microdroplets may be removed with microdropletssorting. For example, as described in Example 1, a drop maker mayoperate close to the dripping-to-jetting transition such that, in theabsence of a cell, 8 μm drops are formed; by contrast, when a cell ispresent the disturbance created in the flow will trigger the breakup ofthe jet, forming drops 25 μm in diameter. The device may thus produce abi-disperse population of empty 8 μm drops and single-cell containing 25μm drops, which may then be sorted by size using, e.g., a hydrodynamicsorter to recover only the larger, single-cell containing drops.

Passive sorters of interest include hydrodynamic sorters, which sortmicrodroplets into different channels according to size, based on thedifferent ways in which small and large microdroplets travel through themicrofluidic channels. Also of interest are bulk sorters, a simpleexample of which is a tube containing microdroplets of different mass ina gravitational field. By centrifuging, agitating, and/or shaking thetube, lighter microdroplets that are more buoyant will naturally migrateto the top of the container. Microdroplets that have magnetic propertiescould be sorted in a similar process, except by applying a magneticfield to the container, towards which microdroplets with magneticproperties will naturally migrate according to the magnitude of thoseproperties. A passive sorter as used in the subject methods may alsoinvolve relatively large channels that will sort large numbers ofmicrodroplets simultaneously based on their flow properties.

Picoinjection can also be used to change the electrical properties ofthe microdroplets, e.g., drops. This could be used, for example, tochange the conductivity of the microdroplets by adding ions, which couldthen be used to sort them, for example, using dielectrophoresis.Alternatively, picoinjection can also be used to charge themicrodroplets, e.g., drops. This could be achieved by injecting a fluidinto the microdroplets that is charged, so that after injection, themicrodroplets would be charged. This would produce a collection ofmicrodroplets in which some were charged and others not, and the chargedmicrodroplets could then be extracted by flowing them through a regionof electric field, which will deflect them based on their charge amount.By injecting different amounts of liquid by modulating thepiocoinjection, or by modulating the voltage to inject different chargesfor affixed injection volume, the final charge on the microdropletscould be adjusted, to produce microdroplets with different charge. Thesewould then be deflected by different amounts in the electric fieldregion, allowing them to be sorted into different containers.

Flow cytometry (FC) may be utilized as an alternative to on-chipmicrodroplet sorting in any of the methods described herein. Such amethod, along with devices which may be utilized in the practice of themethod, are described in Lim and Abate, Lab Chip, 2013, 13, 4563-4572;the disclosure of which is incorporated herein by reference in itsentirety and for all purposes. Briefly, microdroplets, e.g., drops, maybe formed and manipulated, e.g., using techniques like splitting andpicoinjection as described herein, resulting in single emulsions. Thesesingle emulsions may then be double emulsified, e.g., using one or moredevices as described in Lim and Abate, Lab Chip, 2013, 13, 4563-4572.The double emulsions may then be analyzed via FC, e.g., FACS.

A device which may be utilized to form double emulsions suitable for FCanalysis and the characterization and application thereof is describedin greater detail herein with reference to FIGS. 38-55 and Example 9. Ageneral workflow scheme for an embodiment including sorting via FACS isprovided in FIG. 70. Although specific microfluidic steps are listed,e.g., picoinjection, drop merger, etc., these are merely exemplary andit should be noted that any of the microfluidic manipulations describedherein may be utilized in connection with such a double-emulsion/FACSsorting scheme.

As described herein, in some embodiments, a coaxial flow-focusing devicemay be utilized to prepare double emulsions suitable for FACS analysis.The device may include a channel which is, e.g., approximately 50 μmtall, into which single emulsion drops are introduced as a close pack;close packing minimizes interstitial oil, allowing the formation ofthin-shelled double emulsions. The double emulsification junctionincludes a channel taller and wider than the single emulsion channel;aqueous carrier fluid is introduced into the Y-shaped channel, as shownin FIGS. 38 and 40. The single emulsion channel is centered horizontallyand vertically in the carrier phase channel; when the aqueous carrierphase is introduced at a sufficient velocity, this geometry ensures thatthe oil encapsulating the single emulsion lifts from the walls, forminga “cone” suspended in the flowing aqueous phase, as shown in FIGS. 38and 40. This non-planar geometry allows for the formation of doubleemulsions in a device that is uniformly hydrophobic.

Downstream of the cone is a constriction centered vertically andhorizontally in the channel, as shown in the schematic of FIG. 38. Thisfeature allows for the formation of thin-shelled double emulsions withjust one core: as the cone extends into the constriction, it ishydrodynamically focused by the rushing carrier phase; this generatessufficient shear to rip individual drops from the tip of the cone, asillustrated in FIG. 38. Without the constriction, the double emulsionswould likely contain multiple cores.

Suitable Subjects

The subject methods may be applied to biological samples taken from avariety of different subjects. In many embodiments the subjects are“mammals” or “mammalian”, where these terms are used broadly to describeorganisms which are within the class mammalia, including the orderscarnivore (e.g., dogs and cats), rodentia (e.g., mice, guinea pigs, andrats), and primates (e.g., humans, chimpanzees, and monkeys). In manyembodiments, the subjects are humans. The subject methods may be appliedto human subjects of both genders and at any stage of development (i.e.,neonates, infant, juvenile, adolescent, adult), where in certainembodiments the human subject is a juvenile, adolescent or adult. Whilethe present invention may be applied to a human subject, it is to beunderstood that the subject methods may also be carried-out on otheranimal subjects (that is, in “non-human subjects”) such as, but notlimited to, birds, mice, rats, dogs, cats, livestock and horses.Accordingly, it is to be understood that any subject in need ofassessment according to the present disclosure is suitable.

Moreover, suitable subjects include those who have and those who havenot been diagnosed with a condition, such as cancer. Suitable subjectsinclude those that are and are not displaying clinical presentations ofone or more cancers. In certain aspects, a subject may one that may beat risk of developing cancer, due to one or more factors such as familyhistory, chemical and/or environmental exposure, genetic mutation(s)(e.g., BRCA1 and/or BRCA2 mutation), hormones, infectious agents,radiation exposure, lifestyle (e.g., diet and/or smoking), presence ofone or more other disease conditions, and the like.

As described more fully above, a variety of different types ofbiological samples may be obtained from such subjects. In certainembodiments, whole blood is extracted from a subject. When desired,whole blood may be treated prior to practicing the subject methods, suchas by centrifugation, fractionation, purification, and the like. Thevolume of the whole blood sample that is extracted from a subject may be100 mL or less, e.g., about 100 mL or less, about 50 mL or less, about30 mL or less, about 15 mL or less, about 10 mL or less, about 5 mL orless, or about 1 mL or less.

The subject methods and devices provided herein are compatible with bothfixed and live cells. In certain embodiments, the subject methods anddevices are practiced with live cells. In other embodiments, the subjectmethods and devices are practiced with fixed cells. Fixing a cellularsample allows for the sample to be washed to extract small molecules andlipids that may interfere with downstream analysis. Further, fixing andpermeabilizing cells allows the cells to be stained with antibodies forsurface proteins as well as intracellular proteins. Combined with theRT-PCR methods described herein, such staining can be used to achievehigh levels of multiplexing because the antibodies are localized to thecell sample, while RT-PCR products are free within a microdroplet. Sucha configuration allows for dyes of the same color to be used forantibodies and for amplicons produced by RT-PCR. Any suitable method canbe used to fix cells, including but not limited to, fixing usingformaldehyde, methanol and/or acetone.

RT-PCR carried out on a fixed cell encapsulated in a microdroplet can becarried out by first diluting the microdroplet and performing the RT-PCRreaction on a sample of the diluted microdroplet. Such dilution of thecellular sample can help to limit any cellular compounds that wouldinterfere with RT-PCR. In other embodiments, the RT-PCR reagents areadded directly to the microdroplet containing the fixed cell in a “onepot” reaction without any dilution of sample. In certain embodiments,fixed cells are solubilized prior to the RT-PCR using proteases anddetergents.

Genotyping Cells

As summarized above, aspects of the invention also include methods forgenotyping components from biological samples. By “genotyping” it ismeant the detection of two or more oligonucleotides (e.g., oncogenes) ina particular cell. Aspects include methods for genotyping cells, e.g.,tumor cells, including CTCs.

In certain such aspects, the methods involve encapsulating in amicrodroplet a cell obtained from a subject's blood sample, wherein onecell is present in the microdroplet; introducing a lysing agent into themicrodroplet and incubating the microdroplet under conditions effectivefor cell lysis; introducing polymerase chain reaction (PCR) reagents anda plurality PCR primers into the microdroplet, and incubating themicrodroplet under conditions allowing for PCR amplification to producePCR amplification products, wherein the plurality of PCR primers includeone or more primers that each hybridize to one or more oncogenes;introducing a plurality of probes into the microdroplet, wherein theprobes hybridize to one or more mutations of interest and fluoresce atdifferent wavelengths; and detecting the presence or absence of specificPCR amplification products by detection of fluorescence of a probe,wherein detection of fluorescence indicates the presence of the PCRamplification products; wherein one or more of steps are performed undermicrofluidic control.

In other aspects, the methods may involve encapsulating in amicrodroplet a cell obtained from a subject's blood sample, wherein onecell is present in the microdroplet; introducing a lysing agent into themicrodroplet and incubating the microdroplet under conditions effectivefor cell lysis; introducing polymerase chain reaction (PCR) reagents anda plurality PCR primers into the microdroplet, and incubating themicrodroplet under conditions allowing for PCR amplification to producePCR amplification products, wherein the plurality of PCR primers includeone or more primers that each hybridize to one or more oncogenes, saidprimers including forward primers including a label, and reverse primersincluding a capture sequence; introducing a fluorescent bead into themicrodroplet, wherein the bead includes a nucleotide sequencecomplementary to a capture sequence; and detecting the presence orabsence of the PCR amplification products by detection of fluorescenceof the bead and fluorescence of a primer, wherein detection offluorescence indicates the presence of the PCR amplification products;wherein one or more of steps are performed under microfluidic control.

In practicing the methods for genotyping cells, any variants to thegeneral steps described herein, such as the number of primers that maybe added, the manner in which reagents are added, suitable subjects, andthe like, may be made.

Detecting Cancer

Methods according to the present invention also involve methods fordetecting cancer. Such methods may include encapsulating in amicrodroplet oligonucleotides obtained from a biological sample from thesubject, wherein at least one oligonucleotide is present in themicrodroplet; introducing polymerase chain reaction (PCR) reagents, adetection component, and a plurality of PCR primers into themicrodroplet and incubating the microdroplet under conditions allowingfor PCR amplification to produce PCR amplification products, wherein theplurality of PCR primers include one or more primers that each hybridizeto one or more oncogenes; and detecting the presence or absence of thePCR amplification products by detection of the detection component,wherein detection of the detection component indicates the presence ofthe PCR amplification products.

Detection of one or more PCR amplification products corresponding to oneor more oncogenes may be indicative that the subject has cancer. Thespecific oncogenes that are added to the microdroplet may vary. Incertain aspects, the oncogene(s) may be specific for a particular typeof cancer, e.g., breast cancer, colon cancer, and the like.

Moreover, in practicing the subject methods the biological sample fromwhich the components are to be detected may vary, and may be based atleast in part on the particular type of cancer for which detection issought. For instance, breast tissue may be used as the biological samplein certain instances, if it is desired to determine whether the subjecthas breast cancer, and the like.

In practicing the methods for detecting cancer, any variants to thegeneral steps described herein, such as the number of primers that maybe added, the manner in which reagents are added, suitable subjects, andthe like, may be made.

Devices

As indicated above, embodiments of the invention employ microfluidicsdevices. Microfluidics devices of this invention may be characterized invarious ways. In certain embodiments, for example, microfluidics deviceshave at least one “micro” channel. Such channels may have at least onecross-sectional dimension on the order of a millimeter or smaller (e.g.,less than or equal to about 1 millimeter). Obviously for certainapplications, this dimension may be adjusted; in some embodiments the atleast one cross-sectional dimension is about 500 micrometers or less. Insome embodiments, again as applications permit, the cross-sectionaldimension is about 100 micrometers or less (or even about 10 micrometersor less—sometimes even about 1 micrometer or less). A cross-sectionaldimension is one that is generally perpendicular to the direction ofcenterline flow, although it should be understood that when encounteringflow through elbows or other features that tend to change flowdirection, the cross-sectional dimension in play need not be strictlyperpendicular to flow. It should also be understood that in someembodiments, a micro-channel may have two or more cross-sectionaldimensions such as the height and width of a rectangular cross-sectionor the major and minor axes of an elliptical cross-section. Either ofthese dimensions may be compared against sizes presented here. Note thatmicro-channels employed in this invention may have two dimensions thatare grossly disproportionate—e.g., a rectangular cross-section having aheight of about 100-200 micrometers and a width on the order or acentimeter or more. Of course, certain devices may employ channels inwhich the two or more axes are very similar or even identical in size(e.g., channels having a square or circular cross-section).

In some embodiments, microfluidic devices of this invention arefabricated using microfabrication technology. Such technology iscommonly employed to fabricate integrated circuits (ICs),microelectromechanical devices (MEMS), display devices, and the like.Among the types of microfabrication processes that can be employed toproduce small dimension patterns in microfluidic device fabrication arephotolithography (including X-ray lithography, e-beam lithography,etc.), self-aligned deposition and etching technologies, anisotropicdeposition and etching processes, self-assembling mask formation (e.g.,forming layers of hydrophobic-hydrophilic copolymers), etc.

In view of the above, it should be understood that some of theprinciples and design features described herein can be scaled to largerdevices and systems including devices and systems employing channelsreaching the millimeter or even centimeter scale channel cross-sections.Thus, when describing some devices and systems as “microfluidic,” it isintended that the description apply equally, in certain embodiments, tosome larger scale devices.

When referring to a microfluidic “device” it is generally intended torepresent a single entity in which one or more channels, reservoirs,stations, etc. share a continuous substrate, which may or may not bemonolithic. A microfluidics “system” may include one or moremicrofluidic devices and associated fluidic connections, electricalconnections, control/logic features, etc. Aspects of microfluidicdevices include the presence of one or more fluid flow paths, e.g.,channels, having dimensions as discussed herein.

In certain embodiments, microfluidic devices of this invention provide acontinuous flow of a fluid medium. Fluid flowing through a channel in amicrofluidic device exhibits many interesting properties. Typically, thedimensionless Reynolds number is extremely low, resulting in flow thatalways remains laminar. Further, in this regime, two fluids joining willnot easily mix, and diffusion alone may drive the mixing of twocompounds.

Various features and examples of microfluidic device components suitablefor use with this invention will now be described.

Substrate

Substrates used in microfluidic systems are the supports in which thenecessary elements for fluid transport are provided. The basic structuremay be monolithic, laminated, or otherwise sectioned. Commonly,substrates include one or more microchannels serving as conduits formolecular libraries and reagents (if necessary). They may also includeinput ports, output ports, and/or features to assist in flow control.

In certain embodiments, the substrate choice may be dependent on theapplication and design of the device. Substrate materials are generallychosen for their compatibility with a variety of operating conditions.Limitations in microfabrication processes for a given material are alsorelevant considerations in choosing a suitable substrate. Usefulsubstrate materials include, e.g., glass, polymers, silicon, metal, andceramics.

Polymers are standard materials for microfluidic devices because theyare amenable to both cost effective and high volume production. Polymerscan be classified into three categories according to their moldingbehavior: thermoplastic polymers, elastomeric polymers and duroplasticpolymers. Thermoplastic polymers can be molded into shapes above theglass transition temperature, and will retain these shapes after coolingbelow the glass transition temperature. Elastomeric polymers can bestretched upon application of an external force, but will go back tooriginal state once the external force is removed. Elastomers do notmelt before reaching their decomposition temperatures. Duroplasticpolymers have to be cast into their final shape because they soften alittle before the temperature reaches their decomposition temperature.

Among the polymers that may be used in microfabricated device of thisinvention are poly(dimethylsiloxane) (PDMS), polyamide (PA),polybutylenterephthalate (PBT), polycarbonate (PC), polyethylene (PE),polymethylmethacrylate (PMMA), polyoxymethylene (POM), polypropylene(PP), polyphenylenether (PPE), polystyrene (PS) and polysulphone (PSU).The chemical and physical properties of polymers can limit their uses inmicrofluidics devices. Specifically in comparison to glass, the lowerresistance against chemicals, the aging, the mechanical stability, andthe UV stability can limit the use of polymers for certain applications.

Glass, which may also be used as the substrate material, has specificadvantages under certain operating conditions. Since glass is chemicallyinert to most liquids and gases, it is particularly appropriate forapplications employing certain solvents that have a tendency to dissolveplastics. Additionally, its transparent properties make glassparticularly useful for optical or UV detection.

Surface Treatments and Coatings

Surface modification may be useful for controlling the functionalmechanics (e.g., flow control) of a microfluidic device. For example, itmay be advantageous to keep fluidic species from adsorbing to channelwalls or for attaching antibodies to the surface for detection ofbiological components.

Polymer devices in particular tend to be hydrophobic, and thus loadingof the channels may be difficult. The hydrophobic nature of polymersurfaces also make it difficult to control electroosmotic flow (EOF).One technique for coating polymer surface is the application ofpolyelectrolyte multilayers (PEM) to channel surfaces. PEM involvesfilling the channel successively with alternating solutions of positiveand negative polyelectrolytes allowing for multilayers to formelectrostatic bonds. Although the layers typically do not bond to thechannel surfaces, they may completely cover the channels even afterlong-term storage. Another technique for applying a hydrophilic layer onpolymer surfaces involves the UV grafting of polymers to the surface ofthe channels. First grafting sites, radicals, are created at the surfaceby exposing the surface to UV irradiation while simultaneously exposingthe device to a monomer solution. The monomers react to form a polymercovalently bonded at the reaction site.

Glass channels generally have high levels of surface charge, therebycausing proteins to adsorb and possibly hindering separation processes.In some situations, it may be advantageous to apply apolydimethylsiloxane (PDMS) and/or surfactant coating to the glasschannels. Other polymers that may be employed to retard surfaceadsorption include polyacrylamide, glycol groups, polysiloxanes,glyceroglycidoxypropyl, poly(ethyleneglycol) and hydroxyethylatedpoly(ethyleneimine). Furthermore, for electroosmotic devices it isadvantageous to have a coating bearing a charge that is adjustable inmagnitude by manipulating conditions inside of the device (e.g. pH). Thedirection of the flow can also be selected based on the coating sincethe coating can either be positively or negatively charged.

Specialized coatings can also be applied to immobilize certain specieson the channel surface—this process is known by those skilled in the artas “functionalizing the surface.” For example, a polymethylmethacrylate(PMMA) surface may be coated with amines to facilitate attachment of avariety of functional groups or targets. Alternatively, PMMA surfacescan be rendered hydrophilic through an oxygen plasma treatment process.

Microfluidic Elements

Microfluidic systems can contain a number of microchannels, valves,pumps, reactors, mixers and other components. Some of these componentsand their general structures and dimensions are discussed below.

Various types of valves can be used for flow control in microfluidicdevices of this invention. These include, but are not limited to passivevalves and check valves (membrane, flap, bivalvular, leakage, etc.).Flow rate through these valves are dependent on various physicalfeatures of the valve such as surface area, size of flow channel, valvematerial, etc. Valves also have associated operational and manufacturingadvantages/disadvantages that should be taken into consideration duringdesign of a microfluidic device.

Micropumps as with other microfluidic components are subjected tomanufacturing constraints. Typical considerations in pump design includetreatment of bubbles, clogs, and durability. Micropumps currentlyavailable include, but are not limited to electric equivalent pumps,fixed-stroke microdisplacement, peristaltic micromembrane and pumps withintegrated check valves.

Macrodevices rely on turbulent forces such as shaking and stirring tomix reagents. In comparison, such turbulent forces are not practicallyattainable in microdevices, mixing in microfluidic devices is generallyaccomplished through diffusion. Since mixing through diffusion can beslow and inefficient, microstructures are often designed to enhance themixing process. These structures manipulate fluids in a way thatincreases interfacial surface area between the fluid regions, therebyspeeding up diffusion. In certain embodiments, microfluidic mixers areemployed. Such mixers may be provide upstream from (and in some casesintegrated with) a microfluidic separation device of this invention.

Micromixers may be classified into two general categories: active mixersand passive mixers. Active mixers work by exerting active control overflow regions (e.g. varying pressure gradients, electric charges, etc.).Passive mixers do not require inputted energy and use only “fluiddynamics” (e.g. pressure) to drive fluid flow at a constant rate. Oneexample of a passive mixer involves stacking two flow streams on top ofone another separated by a plate. The flow streams are contacted witheach other once the separation plate is removed. The stacking of the twoliquids increases contact area and decreases diffusion length, therebyenhancing the diffusion process. Mixing and reaction devices can beconnected to heat transfer systems if heat management is needed. As withmacro-heat exchangers, micro-heat exchanges can either have co-current,counter-current, or cross-flow flow schemes. Microfluidic devicesfrequently have channel widths and depths between about 10 μm and about10 cm. A common channel structure includes a long main separationchannel, and three shorter “offshoot” side channels terminating ineither a buffer, sample, or waste reservoir. The separation channel canbe several centimeters long, and the three side channels usually areonly a few millimeters in length. Of course, the actual length,cross-sectional area, shape, and branch design of a microfluidic devicedepends on the application as well other design considerations such asthroughput (which depends on flow resistance), velocity profile,residence time, etc.

Microfluidic devices described herein may include electric fieldgenerators to perform certain steps of the methods described herein,including, but not limited to, picoinjection, droplet coalescence,selective droplet fusion, and droplet sorting. In certain embodiments,the electric fields are generated using metal electrodes. In particularembodiments, electric fields are generated using liquid electrodes. Incertain embodiments, liquid electrodes include liquid electrode channelsfilled with a conducting liquid (e.g. salt water or buffer) and situatedat positions in the microfluidic device where an electric field isdesired. In particular embodiments, the liquid electrodes are energizedusing a power supply or high voltage amplifier. In some embodiments, theliquid electrode channel includes an inlet port so that a conductingliquid can be added to the liquid electrode channel. Such conductingliquid may be added to the liquid electrode channel, for example, byconnecting a tube filled with the liquid to the inlet port and applyingpressure. In particular embodiments, the liquid electrode channel alsoincludes an outlet port for releasing conducting liquid from thechannel. In particular embodiments, the liquid electrodes are used inpicoinjection, droplet coalescence, selective droplet fusion, and/ordroplet sorting aspects of a microfluidic device described herein.Liquid electrodes may find use, for example, where a material to beinjected via application of an electric field is not charged.

Liquid electrodes as described herein also have applicability outside ofthe specific microfluidic device applications discussed herein. Forexample, liquid electrodes may be utilized in a variety of devices inwhich metal electrodes are generally used. In addition, liquidelectrodes may be particularly well suited for use in flexible devices,such as devices that are designed to be worn on the body and/or devicesthat must flex as a result of their operation.

In certain embodiments, one or more walls of a microfluidic devicechannel immediately down-stream of a junction with one or more of aninput microchannel, pairing microchannel and/or picoinjectionmicrochannel includes one or more ridges. Such ridges in the walls ofthe microchannel are configured to trap a layer of a suitable phase,e.g., a suitable hydrophobic phase (e.g., oil) and thereby prevent animmiscible phase, e.g., an aqueous phase, from touching the walls of themicrochannel, which can cause wetting of the channel walls. Such wettingmay be undesirable as it may lead to unpredictable drop formation and/orallow fluids to transfer between drops, leading to contamination. Incertain embodiments, the ridges allow for the formation of drops athigher flow rate ratios R (Q_(aq)/Q_(sum)).

In certain embodiments, the width of one or more of the microchannels ofthe microfluidic device (e.g., input microchannel, pairing microchannel,pioinjection microchannel, and/or a flow channel upstream or downstreamof one or more of these channels) is 100 microns or less, e.g., 90microns or less, 80 microns or less, 70 microns or less, 60 microns orless, 50 microns or less, e.g., 45 microns or less, 40 microns or less,39 microns or less, 38 microns or less, 37 microns or less, 36 micronsor less, 35 microns or less, 34 microns or less, 33 microns or less, 32microns or less, 31 microns or less, 30 microns or less, 29 microns orless, 28 microns or less, 27 microns or less, 26 microns or less, 25microns or less, 20 microns or less, 15 microns or less, or 10 micronsor less. In some embodiments, the width of one or more of the abovemicrochannels is from about 10 microns to about 15 microns, from about15 microns to about 20 microns, from about 20 microns to about 25microns, from about 25 microns to about 30 microns, from about 30microns to about 35 microns, from about 35 microns to about 40 microns,from about 40 microns to about 45 microns, or from about 45 microns toabout 50 microns, from about 50 microns to about 60 microns, from about60 microns to about 70 microns, from about 70 microns to about 80microns, from about 80 microns to about 90 microns, or from about 90microns to about 100 microns.

In certain embodiments, the base of each of the one or more ridges isfrom about 10 microns to about 20 microns in length, e.g., from about 11to about 19 microns in length, from about 12 to about 18 microns inlength, from about 13 to about 17 microns in length, from about 14 toabout 16 microns in length, or about 15 microns in length.

In certain embodiments, the peak of each of the one or more ridges has awidth of about 1 to about 10 microns, e.g., from about 1 to about 9microns, from about 2 to about 8 microns, from about 3 to about 7microns, from about 4 to about 6 microns, or about 5 microns. In certainembodiments, the peak of each of the one or more ridges has a width offrom about 1 micron to about 2 microns, from about 2 microns to about 3microns, from about 3 microns to about 4 microns, from about 4 micronsto about 5 microns, from about 5 microns to about 6 microns, from about6 microns to about 7 microns, from about 7 microns to about 8 microns,from about 8 microns to about 9 microns, or from about 9 microns toabout 10 microns.

In certain embodiments, the height of each of the one or more ridges isfrom about 5 microns to about 15 microns, e.g., about 6 microns to about14 microns, about 7 microns to about 13 microns, about 8 microns toabout 12 microns, about 9 microns to about 11 microns, or about 10microns.

In certain embodiments, the ratio of the base of each of the one or moreridges to the height of each of the one or more ridges is from about1.0:0.75 to about 0.75:1.0. In certain embodiments, the ratio of thebase of each of the one or more ridges to the width of the peak of eachof the one or more ridges is about 1.0:0.5 to about 1.0:0.1, e.g, fromabout 1.0:0.2, from about 1.0:0.3, or from about 1.0:0.4.

In certain embodiments, the ratio of the base of each of the one or moreridges to the height of each of the one or more ridges to the width ofthe peak of the one or more ridges is about 1:0.75:0.5.

In certain embodiments, a channel as described herein is provided with aplurality of ridges which extend for a distance along the channel wall.This distance may be, for example, from about 50 microns to about 500microns, e.g., from about 50 microns to about 450 microns, from about100 microns to about 400 microns, from about 150 microns to about 350microns, from about 200 microns to about 300 microns, or about 250microns. In certain embodiments, a plurality of ridges may be providedwhich extend for a distance along the channel wall, wherein the ratiobetween the distance along the channel wall and the width of the channelis from about 10:1 to about 1:2, e.g., about 10:1, about 9:1, about 8:1,about 7:1, about 6:1 about 5:1, about 4:1, about 3:1, about 2:1, about1:1, or about 1:2.

It should be noted that one or more of the various dimensions discussedabove may be scaled up or down as appropriate for a particularapplication, for example each of the above dimensions may be scaled upor down by a factor of 2, 5, 10 or more as appropriate.

In some embodiments, one or more channel junctions, e.g., one or moredroplet forming junctions, such as a picoinjector junction, include a“step-down” structure. This is depicted, for example, in FIG. 26,wherein the portion of the flow channel at the picoinjector junction anddownstream of the picoinjector junction is wider than the portion of theflow channel upstream of the picoinjector junction. This step-downstructure facilitates the pinching-off of droplets and thus facilitatesdroplet formation. The step size may be chosen based on the desired sizeof the droplet to be formed, with larger steps creating larger droplets.Such structures may also help to avoid dripping of material from thepicoinjector following injection from the picoinjector into a droplet.In some embodiments, the width of the flow channel at the picoinjectorjunction and downstream of the picoinjector junction is from about 5% toabout 50% wider than the width of the flow channel immediately upstreamof the picoinjector junction, e.g., about 5 to about 10% wider, about 10to about 20% wider, about 20 to about 30% wider, about 30 to about 40%wider or about 40 to about 50% wider.

Methods of Fabrication

Microfabrication processes differ depending on the type of materialsused in the substrate and the desired production volume. For smallvolume production or prototypes, fabrication techniques include LIGA,powder blasting, laser ablation, mechanical machining, electricaldischarge machining, photoforming, etc. Technologies for mass productionof microfluidic devices may use either lithographic or master-basedreplication processes. Lithographic processes for fabricating substratesfrom silicon/glass include both wet and dry etching techniques commonlyused in fabrication of semiconductor devices. Injection molding and hotembossing typically are used for mass production of plastic substrates.

Glass, Silicon and Other “Hard” Materials (Lithography, Etching,Deposition)

The combination of lithography, etching and deposition techniques may beused to make microcanals and microcavities out of glass, silicon andother “hard” materials. Technologies based on the above techniques arecommonly applied in for fabrication of devices in the scale of 0.1-500micrometers.

Microfabrication techniques based on current semiconductor fabricationprocesses are generally carried out in a clean room. The quality of theclean room is classified by the number of particles <4 μm in size in acubic inch. Typical clean room classes for MEMS microfabrication are1000 to 10000.

In certain embodiments, photolithography may be used inmicrofabrication. In photolithography, a photoresist that has beendeposited on a substrate is exposed to a light source through an opticalmask. Conventional photoresist methods allow structural heights of up to10-40 μm. If higher structures are needed, thicker photoresists such asSU-8, or polyimide, which results in heights of up to 1 mm, can be used.

After transferring the pattern on the mask to the photoresist-coveredsubstrate, the substrate is then etched using either a wet or dryprocess. In wet etching, the substrate—area not protected by the mask—issubjected to chemical attack in the liquid phase. The liquid reagentused in the etching process depends on whether the etching is isotropicor anisotropic. Isotropic etching generally uses an acid to formthree-dimensional structures such as spherical cavities in glass orsilicon. Anisotropic etching forms flat surfaces such as wells andcanals using a highly basic solvent. Wet anisotropic etching on siliconcreates an oblique channel profile.

Dry etching involves attacking the substrate by ions in either a gaseousor plasma phase. Dry etching techniques can be used to createrectangular channel cross-sections and arbitrary channel pathways.Various types of dry etching that may be employed including physical,chemical, physico-chemical (e.g., RIE), and physico-chemical withinhibitor. Physical etching uses ions accelerated through an electricfield to bombard the substrate's surface to “etch” the structures.Chemical etching may employ an electric field to migrate chemicalspecies to the substrate's surface. The chemical species then reactswith the substrate's surface to produce voids and a volatile species.

In certain embodiments, deposition is used in microfabrication.Deposition techniques can be used to create layers of metals,insulators, semiconductors, polymers, proteins and other organicsubstances. Most deposition techniques fall into one of two maincategories: physical vapor deposition (PVD) and chemical vapordeposition (CVD). In one approach to PVD, a substrate target iscontacted with a holding gas (which may be produced by evaporation forexample). Certain species in the gas adsorb to the target's surface,forming a layer constituting the deposit. In another approach commonlyused in the microelectronics fabrication industry, a target containingthe material to be deposited is sputtered with using an argon ion beamor other appropriately energetic source. The sputtered material thendeposits on the surface of the microfluidic device. In CVD, species incontact with the target react with the surface, forming components thatare chemically bonded to the object. Other deposition techniquesinclude: spin coating, plasma spraying, plasma polymerization, dipcoating, casting and Langmuir-Blodgett film deposition. In plasmaspraying, a fine powder containing particles of up to 100 μm in diameteris suspended in a carrier gas. The mixture containing the particles isaccelerated through a plasma jet and heated. Molten particles splatteronto a substrate and freeze to form a dense coating. Plasmapolymerization produces polymer films (e.g. PMMA) from plasma containingorganic vapors.

Once the microchannels, microcavities and other features have beenetched into the glass or silicon substrate, the etched features areusually sealed to ensure that the microfluidic device is “watertight.”When sealing, adhesion can be applied on all surfaces brought intocontact with one another. The sealing process may involve fusiontechniques such as those developed for bonding between glass-silicon,glass-glass, or silicon-silicon.

Anodic bonding can be used for bonding glass to silicon. A voltage isapplied between the glass and silicon and the temperature of the systemis elevated to induce the sealing of the surfaces. The electric fieldand elevated temperature induces the migration of sodium ions in theglass to the glass-silicon interface. The sodium ions in theglass-silicon interface are highly reactive with the silicon surfaceforming a solid chemical bond between the surfaces. The type of glassused should ideally have a thermal expansion coefficient near that ofsilicon (e.g. Pyrex Corning 7740).

Fusion bonding can be used for glass-glass or silicon-silicon sealing.The substrates are first forced and aligned together by applying a highcontact force. Once in contact, atomic attraction forces (primarily vander Waals forces) hold the substrates together so they can be placedinto a furnace and annealed at high temperatures. Depending on thematerial, temperatures used ranges between about 600 and 1100° C.

Polymers/Plastics

A number of techniques may be employed for micromachining plasticsubstrates in accordance with embodiments of this invention. Among theseare laser ablation, stereolithography, oxygen plasma etching, particlejet ablation, and microelectro-erosion. Some of these techniques can beused to shape other materials (glass, silicon, ceramics, etc.) as well.

To produce multiple copies of a microfluidic device, replicationtechniques are employed. Such techniques involve first fabricating amaster or mold insert containing the pattern to be replicated. Themaster is then used to mass-produce polymer substrates through polymerreplication processes.

In the replication process, the master pattern contained in a mold isreplicated onto the polymer structure. In certain embodiments, a polymerand curing agent mix is poured onto a mold under high temperatures.After cooling the mix, the polymer contains the pattern of the mold, andis then removed from the mold. Alternatively, the plastic can beinjected into a structure containing a mold insert. In microinjection,plastic heated to a liquid state is injected into a mold. Afterseparation and cooling, the plastic retains the mold's shape.

PDMS (polydimethylsiloxane), a silicon-based organic polymer, may beemployed in the molding process to form microfluidic structures. Becauseof its elastic character, PDMS is well suited for microchannels betweenabout 5 and 500 μm. Specific properties of PDMS make it particularlysuitable for microfluidic purposes:

-   -   1) It is optically clear which allows for visualization of the        flows;    -   2) PDMS when mixed with a proper amount of reticulating agent        has elastomeric qualities that facilitates keeping microfluidic        connections “watertight;”    -   3) Valves and pumps using membranes can be made with PDMS        because of its elasticity;    -   4) Untreated PDMS is hydrophobic, and becomes temporarily        hydrophilic after oxidation of surface by oxygen plasma or after        immersion in strong base; oxidized PDMS adheres by itself to        glass, silicon, or polyethylene, as long as those surfaces were        themselves exposed to an oxygen plasma.    -   5) PDMS is permeable to gas. Filling of the channel with liquids        is facilitated even when there are air bubbles in the canal        because the air bubbles are forced out of the material. But it's        also permeable to non polar-organic solvents.

Microinjection can be used to form plastic substrates employed in a widerange of microfluidic designs. In this process, a liquid plasticmaterial is first injected into a mold under vacuum and pressure, at atemperature greater than the glass transition temperature of theplastic. The plastic is then cooled below the glass transitiontemperature. After removing the mold, the resulting plastic structure isthe negative of the mold's pattern.

Yet another replicating technique is hot embossing, in which a polymersubstrate and a master are heated above the polymer's glass transitiontemperature, Tg (which for PMMA or PC is around 100-180° C.). Theembossing master is then pressed against the substrate with a presetcompression force. The system is then cooled below Tg and the mold andsubstrate are then separated.

Typically, the polymer is subjected to the highest physical forces uponseparation from the mold tool, particularly when the microstructurecontains high aspect ratios and vertical walls. To avoid damage to thepolymer microstructure, material properties of the substrate and themold tool may be taken into consideration. These properties include:sidewall roughness, sidewall angles, chemical interface betweenembossing master and substrate and temperature coefficients. Highsidewall roughness of the embossing tool can damage the polymermicrostructure since roughness contributes to frictional forces betweenthe tool and the structure during the separation process. Themicrostructure may be destroyed if frictional forces are larger than thelocal tensile strength of the polymer. Friction between the tool and thesubstrate may be important in microstructures with vertical walls. Thechemical interface between the master and substrate could also be ofconcern. Because the embossing process subjects the system to elevatedtemperatures, chemical bonds could form in the master-substrateinterface. These interfacial bonds could interfere with the separationprocess. Differences in the thermal expansion coefficients of the tooland the substrate could create addition frictional forces.

Various techniques can be employed to form molds, embossing masters, andother masters containing patterns used to replicate plastic structuresthrough the replication processes mentioned above. Examples of suchtechniques include LIGA (described below), ablation techniques, andvarious other mechanical machining techniques. Similar techniques canalso be used for creating masks, prototypes and microfluidic structuresin small volumes. Materials used for the mold tool include metals, metalalloys, silicon and other hard materials.

Laser ablation may be employed to form microstructures either directlyon the substrate or through the use of a mask. This technique uses aprecision-guided laser, typically with wavelength between infrared andultraviolet. Laser ablation may be performed on glass and metalsubstrates, as well as on polymer substrates. Laser ablation can beperformed either through moving the substrate surface relative to afixed laser beam, or moving the beam relative to a fixed substrate.Various micro-wells, canals, and high aspect structures can be made withlaser ablation.

Certain materials such as stainless steel make very durable mold insertsand can be micromachined to form structures down to the 10-μm range.Various other micromachining techniques for microfabrication existincluding μ-Electro Discharge Machining (μ-EDM), μ-milling, focused ionbeam milling. μ-EDM allows the fabrication of 3-dimensional structuresin conducting materials. In μ-EDM, material is removed by high-frequencyelectric discharge generated between an electrode (cathode tool) and aworkpiece (anode). Both the workpiece and the tool are submerged in adielectric fluid. This technique produces a comparatively roughersurface but offers flexibility in terms of materials and geometries.

Electroplating may be employed for making a replication mold tool/masterout of, e.g., a nickel alloy. The process starts with a photolithographystep where a photoresist is used to defined structures forelectroplating. Areas to be electroplated are free of resist. Forstructures with high aspect ratios and low roughness requirements, LIGAcan be used to produce electroplating forms. LIGA is a German acronymfor Lithographic (Lithography), Galvanoformung (electroplating),Abformung (molding). In one approach to LIGA, thick PMMA layers areexposed to x-rays from a synchrotron source. Surfaces created by LIGAhave low roughness (around 10 nm RMS) and the resulting nickel tool hasgood surface chemistry for most polymers.

As with glass and silicon devices, polymeric microfluidic devices mustbe closed up before they can become functional. Common problems in thebonding process for microfluidic devices include the blocking ofchannels and changes in the physical parameters of the channels.Lamination is one method used to seal plastic microfluidic devices. Inone lamination process, a PET foil (about 30 μm) coated with a meltingadhesive layer (typically 5-10 μm) is rolled with a heated roller, ontothe microstructure. Through this process, the lid foil is sealed ontothe channel plate. Several research groups have reported a bonding bypolymerization at interfaces, whereby the structures are heated andforce is applied on opposite sides to close the channel. But excessiveforce applied may damage the microstructures. Both reversible andirreversible bonding techniques exist for plastic-plastic andplastic-glass interfaces. One method of reversible sealing involvesfirst thoroughly rinsing a PDMS substrate and a glass plate (or a secondpiece of PDMS) with methanol and bringing the surfaces into contact withone another prior to drying. The microstructure is then dried in an ovenat 65° C. for 10 min. No clean room is required for this process.Irreversible sealing is accomplished by first thoroughly rinsing thepieces with methanol and then drying them separately with a nitrogenstream. The two pieces are then placed in an air plasma cleaner andoxidized at high power for about 45 seconds. The substrates are thenbrought into contact with each other and an irreversible seal formsspontaneously.

Other available techniques include laser and ultrasonic welding. Inlaser welding, polymers are joined together through laser-generatedheat. This method has been used in the fabrication of micropumps.Ultrasonic welding is another bonding technique that may be employed insome applications.

It should be noted that while the nucleic acid amplification techniquesdescribed herein are frequently described with reference to polymerasechain reaction (PCR) amplification techniques, such description is notintended to be limiting. In certain embodiments, non-PCR amplificationtechniques may be employed such as various isothermal nucleic acidamplification techniques; e.g., real-time strand displacementamplification (SDA), rolling-circle amplification (RCA) andmultiple-displacement amplification (MDA). Accordingly, wherevertechnically feasible, one or more suitable non-PCR amplificationtechniques, e.g., one or more isothermal nucleic acid amplificationtechniques, may be substituted for one or more of the PCR amplificationtechniques described herein.

Regarding PCR amplification modules, it will be necessary to provide tosuch modules at least the building blocks for amplifying nucleic acids(e.g., ample concentrations of four nucleotides), primers, polymerase(e.g., Taq), and appropriate temperature control programs). Thepolymerase and nucleotide building blocks may be provided in a buffersolution provided via an external port to the amplification module orfrom an upstream source. In certain embodiments, the buffer streamprovided to the sorting module contains some of all the raw materialsfor nucleic acid amplification. For PCR in particular, precisetemperature control of the reacting mixture is extremely important inorder to achieve high reaction efficiency. One method of on-chip thermalcontrol is Joule heating in which electrodes are used to heat the fluidinside the module at defined locations. The fluid conductivity may beused as a temperature feedback for power control.

In certain aspects, the microdroplets, e.g., drops, containing the PCRmix may be flowed through a channel that incubates the droplets underconditions effective for PCR. Flowing the microdroplets through achannel may involve a channel that snakes over various temperature zonesmaintained at temperatures effective for PCR. Such channels may, forexample, cycle over two or more temperature zones, wherein at least onezone is maintained at about 65° C. and at least one zone is maintainedat about 95° C. As the microdroplets move through such zones, theirtemperature cycles, as needed for PCR. The precise number of zones, andthe respective temperature of each zone, may be readily determined bythose of skill in the art to achieve the desired PCR amplification.

In other embodiments, incubating the microdroplets, e.g., drops, mayinvolve the use of a Megadroplet Array. In such a device, an arrayconsists of channels in which the channel ceilings are indented withmillions of circular traps that are about 25 μm in diameter. Drops aredistributed into the trapping channels using distribution plates—largechannels connecting the inlets of the trapping channels (FIG. 12, PanelA). Due to the large size of the distribution channels compared to thetrapping channels—the distribution channels are about 100×500 μm inheight and width, compared to only about 15×100 μm for the droplettrapping channels—the hydrodynamic resistance of the distributionchannels is 1500 times lower than that of the trapping channels; thisensures that the distribution channel fills with drops before thetrapping channels begin to fill, allowing even distribution of the dropsinto the trapping channels. When the drops flow into the trappingchannels, they are slightly pancaked in shape because the verticalheight of the channel is 15 μm, or 10 μm shorter than the drops, asillustrated in FIG. 12, Panel B. When a drop nears a trap, its interfaceadopts a larger, more energetically favorable radius of curvature. Tominimize its surface energy, the drop entirely fills the trap, allowingit to adopt the lowest, most energetically favorable, average radius ofcurvature. After a trap is occupied by a drop, no other drops are ableto enter because the trap is large enough to fit only one drop;additional drops are diverted downstream, to occupy the first vacanttrap they encounter. Because the array is filled using a close-packedemulsion, every trap will be occupied by a drop, since this is the mostenergetically favorable state under low flow conditions. After thedroplet array is filled, oil is injected to remove excess drops and thearray is thermal cycled and imaged.

A variety of different ways can be used to fill the traps of the device.For instance, buoyancy effects and centrifugation can also be used tofill and empty the traps by flipping the device with respect to theearth's gravitational field, since the droplet density is 63% that ofthe fluorocarbon carrier oil. That is, if the drops were heavier thanthe oil phase, then the wells could be imprinted into the “floor” of thedevice so that when the emulsion was flowed over it, the drops wouldsink into the wells. The flow rate of the emulsion could be adjusted tooptimize this and the drop size would be made to be approximately thesame size as the well so that the well could only fit a single drop at atime. In other aspects, the drops could also, or instead, be stored in alarge chamber with no wells.

The device may achieve thermal cycling using a heater consisting of aPeltier plate, heat sink, and control computer (FIG. 12, Panel A; FIG.13). The Peltier plate allows heating and/or cooling the chip above orbelow room temperature by controlling the applied current. To ensurecontrolled and reproducible temperature, a computer monitors thetemperature of the array using integrated temperature probes, andadjusts the applied current to heat and cool as needed. A metallic(e.g., copper) plate allows uniform application of heat and dissipationof excess heat during cooling cycles, enabling cooling from 95° C. to60° C. in under 1 min execution. In order to image microdroplets,certain embodiments may incorporate a scanner bed. In certain aspects,the scanner bed is a Canoscan 9000F scanner bed.

In order to effectively amplify nucleic acids from target components,the microfluidics system may include a cell lysing or viral proteincoat-disrupting module to free nucleic acids prior to providing thesample to an amplification module. Cell lysing modules may rely onchemical, thermal, and/or mechanical means to effect cell lysis. Becausethe cell membrane consists of a lipid double-layer, lysis bufferscontaining surfactants can solubilize the lipid membranes. Typically,the lysis buffer will be introduced directly to a lysis chamber via anexternal port so that the cells are not prematurely lysed during sortingor other upstream process. In cases where organelle integrity isnecessary, chemical lysis methods may be inappropriate. Mechanicalbreakdown of the cell membrane by shear and wear is appropriate incertain applications. Lysis modules relying mechanical techniques mayemploy various geometric features to effect piercing, shearing,abrading, etc. of cells entering the module. Other types of mechanicalbreakage such as acoustic techniques may also yield appropriate lysate.Further, thermal energy can also be used to lyse cells such as bacteria,yeasts, and spores. Heating disrupts the cell membrane and theintracellular materials are released. In order to enable subcellularfractionation in microfluidic systems a lysis module may also employ anelectrokinetic technique or electroporation. Electroporation createstransient or permanent holes in the cell membranes by application of anexternal electric field that induces changes in the plasma membrane anddisrupts the transmembrane potential. In microfluidic electroporationdevices, the membrane may be permanently disrupted, and holes on thecell membranes sustained to release desired intracellular materialsreleased.

Single Cell RT-PCR Microfluidic Device

In another aspect, provided herein is a single cell RT-PCR microfluidicdevice, described in greater detail below with reference to FIG. 32. Incertain embodiments, the single cell RT-PCR microfluidic device includesan input microchannel, which may be coupled to a flow focus drop maker,for introducing microdroplets into the microfluidic device, wherein theflow focus drop maker spaces the microdroplets in the inputmicrochannel, e.g., by a volume of a suitable hydrophobic phase, e.g.,oil, wherein each microdroplet may include a cell lysate sample. Anexemplary embodiment is shown in FIG. 32 (Panel A).

The microfluidic device may further include a pairing microchannel influidic communication with the input microchannel and a dilution bufferdrop maker in fluidic communication with the pairing microchannel. Insuch embodiments, a microdroplet from the input microchannel flows intothe pairing microchannel where the dilution buffer drop maker produces adrop of dilution buffer that is larger than and paired with eachmicrodroplet. In certain embodiments, the dilution buffer drop maker isa T-junction drop maker. An exemplary embodiment is shown in FIG. 32(Panel B).

The microfluidic device may also include a merging microchannel influidic communication with the pairing microchannel, the mergingmicrochannel including an electric field generator positioned inproximity thereto. In such embodiments, the paired microdroplet and dropof dilution buffer enter the merging microchannel from the pairingmicrochannel and are merged upon passing through an electric fieldproduced by the electric field generator to produce a dilutedmicrodroplet. Any suitable electric field generator can be used toproduce the diluted microdroplet. In certain embodiments, the electricfield is created by metal electrodes. In other embodiments, the electricfield is created by liquid electrodes as discussed herein. An exemplaryembodiment is shown in FIG. 32 (Panel C).

The microfluidic device may also include a series of mixingmicrochannels in fluidic communication with the merging microchannel.Such mixing microchannels allow for the mixing of the contents of thediluted microdroplet.

The microfluidic device may also include a drop sampler in fluidiccommunication with the mixing microchannels. Such a drop sampler iscapable of taking a sample of the diluted microdroplet, e.g., to be usedin a subsequent RT-PCR reaction carried out in the microfluidic device.An exemplary embodiment is shown in FIG. 32 (Panel D).

The microfluidic device may also include a picoinjection microchannelincluding a picoinjector, wherein the picoinjection microchannel may bea pressurized microchannel capable of receiving the sample of thediluted microdroplet produced by the drop sampler and allowing thepicoinejctor to picoinject RT-PCR reagents into the sample. In certainembodiments the picoinjection is assisted by an electric field appliedto the picoinjection microchannel. Any electric field generator can beused to create an electric field for picoinjection. In certainembodiments, the electric field is created by metal electrodes. In otherembodiments, the electric field is created by liquid electrodes asdiscussed herein. An exemplary embodiment is shown in FIG. 32 (Panel E).

Samples of the diluted microdroplet that have been picoinjected withRT-PCR reagents can then be subjected to conditions for RT-PCR using anyof the approaches described herein. The single cell RT-PCR microfluidicdevice advantageously allows for the dilution of the cell lysate sampleprior to addition of RT-PCR agents. Such dilution helps in preventinhibition of RT-PCR that may be caused by components of the celllysate. In certain embodiments, the microfluidic device also includes anencapsulating chamber in fluidic communication with the inputmicrochannel, for encapsulating a cell and lysis regeant into amicrodroplet. In such embodiments, the input micochannel is capable ofreceiving the microdroplet from the encapsulating chamber.

Although the above device is described with respect to an RT-PCRreaction, such is for exemplary purposes only. The device could be usedin connection with a variety of other reaction types, including, e.g.,PCR.

EXAMPLES

As can be appreciated from the disclosure provided above, the presentdisclosure has a wide variety of applications. Accordingly, thefollowing examples are put forth so as to provide those of ordinaryskill in the art with a complete disclosure and description of how tomake and use the present invention, and are not intended to limit thescope of what the inventors regard as their invention nor are theyintended to represent that the experiments below are all or the onlyexperiments performed. Those of skill in the art will readily recognizea variety of noncritical parameters that could be changed or modified toyield essentially similar results. Thus, the following examples are putforth so as to provide those of ordinary skill in the art with acomplete disclosure and description of how to make and use the presentinvention, and are not intended to limit the scope of what the inventorsregard as their invention nor are they intended to represent that theexperiments below are all or the only experiments performed. Effortshave been made to ensure accuracy with respect to numbers used (e.g.amounts, temperature, etc.) but some experimental errors and deviationsshould be accounted for.

Example 1: Microfluidic System for Performing Single-Cell PCR Reactions

Device Manufacturing:

The chips were made using the same photolithographic processes inpolydimethylsiloxane as the other devices described above. A generalschematic of the chips is shown in FIG. 1. The general approach carriedout by such chips is depicted in FIG. 6.

Sample Preparation:

5-25 mL whole blood samples were extracted from a subject via syringe.Nucleated cells were separated using on-chip pinched-flow fractionation,as generally described in Lab on a Chip, 2005, 5, 778-784; thedisclosure of which is incorporated herein by reference. Nucleated cellswere collected for subsequent analysis.

PCR Reactions:

The assay requires the execution of an RT-PCR reaction in dropscontaining concentrated cell lysates; however, cell lysates inhibitRT-PCR (FIG. 7). To overcome this inhibition, a protocol has beendeveloped that utilizes proteinase K to digest inhibitory proteins incell lysates. Using proteinase K allows efficient amplification inlysates at concentrations as high as 1 cell in 50 pL, with optimalamplification occurring at 1 cell in 200 pL (FIG. 7). Thus, the systemoperates at this concentration.

Cell encapsulation, lysis, and proteinase K digestion are accomplishedusing an integrated microfluidic system (FIG. 8, Panels 1-3). Cells areco-encapsulated in 70 μm drops (200 pL) with lysis buffer containingnon-ionic detergents and proteinase K using a 30×30 μm flow focusdevice. Importantly, the cells are not exposed to lysis buffer untilthey are encapsulated in drops, ensuring that no lysis occurs prior toencapsulation. This is enabled by the laminar flow conditions in themicrofluidic channels, which ensure that diffusive mixing is negligiblecompared to the convection of the fluids. Following encapsulation, theclose-packed drops move through a 55° C. incubation channel for 20 min,to allow the cells to lyse and the proteinase K to digest inhibitoryproteins. The drops are then split into equally-sized drops using ahierarchical splitter (FIG. 5; FIG. 8, Panel 3), producing drops of theideal small size for picoinjection and Megadroplet Array imaging (FIGS.12-13).

Prior to injection of the RT-PCR reagents and enzymes, the proteinase Kis inactivated by heating the drops to 95° C. for 10 min. The drops arethen injected with an equal volume of 2× primers and RT-PCR reagents(FIG. 9, Panel A). After picoinjection, the emulsion is collected into aPCR tube and thermal cycled. To determine whether a drop contains acancer cell, TaqMan® probes are also included that hybridize to theEpCAM amplicons; this allows the probes to be hydrolyzed by the 5′-3′nuclease activity of Taq DNA polymerase, liberating the 5′ fluorophorefrom the quenching 3′ end modification making the drop fluorescent. Bycontrast, drops not containing cancer cells do not have EpCAM amplicons,so that the TaqMan® probes remain quenched and non-fluorescent (FIG. 4,Panels A-B). Hence, a bright drop relates the presence of an EpCAMpositive cancer cell (FIG. 9, Panels B-C; FIG. 10). The thermocycleddrops are injected into a flow cell 30 μm in height and 54 cm² in area;the narrow vertical gap of the flow cell forces the emulsion into amonolayer, allowing unobstructed epi-fluorescence visualization of everydrop. For the fluorescence imaging, an automated microscope captures amosaic of the entire flow cell and stores the images on a hard drive.The images are processed with custom Matlab code to identify fluorescentdrops and measure their brightness. All data is stored digitally andanalyzed using custom algorithms.

Example 2: Quantitative Multiplexed Assay

To screen more than one gene simultaneously, a multiplexed qPCR reactionmay be utilized. Reactions were initially performed in bulk with PCRtubes to optimize reaction conditions. Using these methods, successfulmultiplexing was achieved during digital droplet RT-PCR for threeTaqMan® probes, EpCAM, CD44 and CD45. An example of this multiplexing isshown in FIG. 11, where EpCAM and CD44 probes were multiplexed in dropscontaining both target transcripts. All PCR primer sets were designed tospan large introns, making these larger genomic PCR products highlyunlikely in multiplex reactions. Additionally, all TaqMan® probes aredesigned to hybridize to exon-exon junctions. The current probe sets donot recognize gDNA.

Single-Cell qPCR with Megadroplet Arrays:

To perform qPCR analysis on single cells, the drops are imaged as theyare thermal cycled. This requires that the drops be held at fixedpositions during thermal cycling so they can be repeatedly imaged. Themicrofluidic system used to prepare the drops was prepared as describedabove and in Example 1. After the drops are formed and loaded with cellsand qPCR reagents, they are introduced into a Megadroplet Array (FIG.12, Panels A-C; FIG. 13). The array consists of channels in which thechannel ceilings are indented with millions of circular traps 25 μm indiameter. When the drops flow into the array, they are slightly pancakedin shape because the vertical height of the flow channel is 15 μm, or 10mm shorter than the drops. When a drop nears a trap, its interfaceadopts a larger, more energetically favorable radius of curvature. Tominimize its surface energy, the drop will entirely fill the trap,allowing it to adopt the lowest, most energetically favorable, averageradius of curvature. The capillary pressure of the drop is severalorders of magnitude larger than the shear exerted by the flow, ensuringthat the drops remain intact and confined in the traps. After a trap isoccupied by a drop, no other drops are able to enter because the trapwill be large enough to fit only one drop; additional drops are diverteddownstream, to occupy the first vacant trap they encounter. The array isfilled using a close-packed emulsion, and thus every trap is occupied bya drop. After the droplet array is filled, oil is injected to removeexcess drops and the array is thermal cycled and imaged.

Thermal System for Temperature Cycling and Imaging:

Once the array is filled with drops and cells, the device is thermalcycled while simultaneously imaging the drops, to obtain thetime-dependent information necessary for qPCR. The thermal cycling isaccomplished using a custom heater consisting of a Peltier plate, heatsink, and control computer (FIG. 13). The Peltier plate permits heatingor cooling the chip above or below room temperature by controlling theapplied current. To ensure controlled and reproducible temperature, acomputer monitors the temperature of the array using integratedtemperature probes, and adjusts the applied current to heat and cool asneeded. A copper-plate allows uniform application of heat anddissipation of excess heat during cooling cycles, enabling cooling from95° C. to 60° C. in under 1 min execution of the qPCR assay in under twohours. To image the droplets during temperature cycling, a customizedCanoscan 9000F scanner bed having a resolution of 9600 dpi by 9600 dpiis utilized. For 10 million hexagonally-packed 25 μm drops (54 cm²), 800million pixels are required at highest resolution. With a resolution of20 pixels per drop, the full image may be captured in 3s. The array isimaged several times per cycle with different excitation and emissionfilters to visualize the different dyes for the multiplexed TaqMan®probes.

Example 3: Electrode-Free Picoinjection of Drops of Microfluidic Drops

Microfluidic devices were fabricated in poly(dimethylsiloxane) (PDMS)using soft photolithographic techniques. The devices had channel heightsof 30 μm, optimal for the picoinjection of water-in-oil droplets thatare 50 μm in diameter. The device design is similar to those describedpreviously by Abate, et al. Proc. Natl. Acad. Sci. U.S.A., 2010, 107,19163; the disclosure of which is incorporated herein by reference. Animportant difference, however, is that the channels for the metal solderelectrodes are removed. Further, a “Faraday Mote”—an empty channelfilled with a conducting aqueous solution—is implemented that runsbetween the injection site and the droplet spacer, as shown in FIG. 15,Panel B. The mote electrically isolates re-injected drops upstream ofthe picoinjection site from electric fields emanating from thepicoinjector, preventing unintended merging. The emulsion that waspicoinjected consists of monodisperse droplets of 3.8 mM fluoresceinsodium salt (C₂₀H₁₀Na₂O₅) dissolved in Milli-Q H₂O. The droplets aresuspended in a carrier oil of Novec HFE-7500 fluorinated oil with 2%(wt/wt) dissolved biocompatible surfactant. The picoinjection fluidsconsist of a dilution series of NaCl ranging from 0 to 500 mM, eachcontaining 3.8 mM fluorescein sodium salt. This range of concentrationsreflects the molarities of dissolved ions present in most biologicalbuffers and reagents. Thus, since in most applications the fluids willalready contain the requisite ions, the technique can be used withoutadding additional reagents to the solutions.

Droplets and carrier oil were introduced via syringe pumps (New Era) andspaced using the same carrier oil and surfactant mixture described above(FIG. 15, Panels A-B). The picoinjection fluid was contained in a BDFalcon tube. Through the cap of the Falcon tube was submerged a wireelectrode into the fluid, as illustrated in FIG. 15, Panel A. Gaps inthe cap were sealed with LocTite UV-cured epoxy. The picoinjection fluidwas charged using a function generator outputting a 10 kHz sinusoidalsignal ranging from 0 to 5 volts. This output was amplified 1000× by aTrek 609E-6 model HV amplifier. The positive output of the amplifier wasattached via an alligator clip to the wire submerged in thepicoinjection fluid. The ground electrode of the amplifier was attachedto the metal needle of a syringe containing a 1 M solution of NaCl,introduced into the Faraday Mote (FIG. 15, Panel A). The two electrodeswere never in electrical contact and the emulsions exiting the devicewere collected into separate, electrically isolated containers to avoida closed circuit and prevent current flow.

The picoinjected reagent was infused into the device through PE-2 tubing(Scientific Commodities) using an air pressure pump (ControlAir Inc.)controlled by custom LabVIEW software. The injection fluid waspressurized such that the oil/water interface at the picoinjectionorifice is in mechanical equilibrium with the droplet channel; thepressure difference across the interface is equal to the Laplacepressure, causing the injection fluid to bulge into the droplet channelwithout budding off and forming its own drops (FIG. 15, Panel C). Forthis device, drops and spacer oil were injected the at flow rates of 200and 400 μL hr⁻¹, respectively. At these flow rates, the picoinjectionfluid interface is in mechanical equilibrium for an applied pressure of˜13 psi. The lengths of the tubing carrying the injection fluid andsolution serving as a Faraday mote was controlled, since longer tubeshave higher electrical resistance and may attenuate the AC signalapplied to trigger picoinjection.

To picoinject drops with reagent, the previously formed monodisperseemulsion was re-injected into the picoinjection device. The emulsion wasintroduced at a high volume-fraction such that there is little carrieroil and the drops are packed together. The packed drops traveled througha narrowing channel that forced them single file. Additional oil withsurfactant is added from two perpendicular channels, spacing the dropsevenly, as shown in FIG. 15, Panel B. A simple T-junction spacer wasalso found to work. The droplets then passed the picoinjector, a narrowchannel containing the reagent to be added. To trigger picoinjection,the voltage signal was applied to the electrode submerged in theinjection fluid, generating an electric field at the picoinjector as thedrops pass the injection site. This caused the drops to coalesce withthe injection fluid. As they traveled past, fluid was injected into themthrough a liquid bridge formed after the two fluids coalesce. Theapplied signal must have zero offset to prevent electrophoreticmigration of charged particles in the solutions. Additionally, thefrequency of the signal must be high enough to ensure that during theact of injecting, the sign of the field switches many times betweenpositive and negative, so that the net charge of the fluid added to thedroplets is approximately zero. This ensured that the droplets leavingthe injector have zero net charge, which was important for ensuring thatthey remain stable. A 10 kHz signal was applied.

To analyze the behavior of the picoinjector, the injection site wasobserved under a microscope. In the absence of an electric field, adistinct boundary was observed between the droplet and the injectionfluid, as shown in FIG. 16, Panel A. When a 250 V signal was applied tothe picoinjector, the boundary vanishes and droplet coalescence isvisible, as demonstrated in FIG. 16, Panel B. Thus, electrification ofthe injection fluid is adequate to trigger picoinjection, demonstratingthat electrically-isolated electrodes are not needed.

To determine if it were possible to vary the injection volume using theapplied voltage, voltage was varied between 0-5000V and the volumechange of the resulting droplets was measured. Injection volume wasquantified with an optical fluorescence detection setup. As the dropspassed a 472 nm wavelength laser focused on the droplet channel ˜1 cmdownstream of the picoinjector, the emitted fluorescence signal from thedissolved fluorescein contained within the drops was amplified by aphotomultiplier tube (PMT) and converted to a voltage signal analyzedwith LabVIEW FPGA. As the drops passed the laser, their fluorescencesignals resembled square waves as a function of time, with amplitudesand widths that corresponded to the drop intensity and length,respectively. The drops had a spherical diameter larger than thedimensions of the channel, causing them to be cylindrical in shape.Thus, the drop volume is approximately linear as a function of length.To calculate the volume fractional (Vf) increase, the ratio of the droplength before and after picoinjection was measured. These measurementswere repeated for a range of applied voltages and molarities of NaCl inthe injection fluid.

The increase in volume was plotted as a function of applied voltage forthree representative molarities of injection fluid in FIG. 17, PanelsA-C. In all cases the injection volume increased with the appliedvoltage, though this effect is most prominent for the 100 mM injectionsolution shown in FIG. 17, Panel A. The dependence of the droplet volumeon the applied voltage may be attributed to the observation that thedroplets are not perfect cylinders as they travel past the picoinjector;instead they have a “bullet” shape, with the leading edge having asmaller radius of curvature than the trailing edge. Consequently, as thedrops pass the picoinjector, the thickness of the oil layer separatingtheir interface from the bulge of the picoinjection fluid decreases. Foran electrically-induced thin-film instability, the threshold voltagerequired to rupture the interface depends on the thickness of the film,decreasing as the film gets thinner. Hence, because the film thicknessdecreases as the drops pass the picoinjector, the moment of coalescencedepends on electric field magnitude: for higher fields it is possible torupture thicker films, leading to picoinjection at an earlier point;conversely, for lower fields thinner films are ruptured, causingpicoinjection to start at a later point. Because the volume injecteddepends on the duration of picoinjection, it therefore also depends onapplied voltage. This is supported by data which shows a dependence onapplied voltage for all molarities (FIG. 17, Panels A-C). It was alsoobserved that the curves relating volume injected to applied voltage arelower for lower molarities, as shown for the 50 mM and 25 mM data inFIG. 17, Panels B and C, respectively. This may be attributable to thefact that lower molarity solutions have a lower conductivity, and canthus attenuate the AC signals used to trigger injection, reducing thevolume injected for a particular applied voltage.

Above 3000V and 100 mM, the injected volume begins to decrease and thevariability in drop size increases. In images of these systems at thesevoltages, it was observed that the picoinjection fluid is no longer heldat equilibrium in the picoinjection orifice, but instead wets thechannel walls and buds off small drops into the flow channel.

To characterize the behavior of the electrode-free picoinjector for allparameters, injection volume was measured as a function of molarity andapplied voltage and the resulting data was plotted on a 2D heat-map(FIG. 18). This data demonstrates that the technique should allowcontrolled picoinjection for most biological buffers, which commonlyhave molarities within the tested range.

To investigate whether the electric fields and currents generated by thehigh-voltage signal may disrupt biomolecules needed for downstreamassays, the picoinjector was used to prepare droplets for an RT-PCRreaction. Drops containing total RNA isolated from an MCF7 human cellline were picoinjected with an RT-PCR reaction mixture containing theenzymes reverse transcriptase (RT) and Taq DNA polymerase.Negative-control drops were injected with a mixture containing noenzymes. Additional non-emulsified positive and negative controlreactions were performed in parallel with the same RT-PCR mixture.Following thermocycling, the emulsions were broken and the amplificationproducts visualized on an ethidium bromide-stained 2% agarose gel. Thepositive control and picoinjected drops showed PCR bands of comparableintensity for the expected 100 bp amplicon length, as visible in FIG.19. In contrast, the negative controls showed no amplification,demonstrating that applying the triggering signal to the picoinjectionfluid is sufficiently biocompatible so as to allow downstream RT-PCRreactions in drops.

Example 4: Coalescing Triple-Emulsions to Add Reagent to Droplets

One step, which may be important in running a droplet reaction, is theability to add reagents to pre-existing drops. As an example, dropaddition might be beneficial if a final drop reaction requires a reagentthat could be denatured in a prior heating step. If no drop-stabilizingsurfactants are used, adding reagent can be as simple as bringing a dropin contact with a second reagent-filled one. Standard drop processingand storage often require surfactant-stabilized drops, however, andlocalized electric fields have been utilized to selectively disrupt andmerge pairs of drops. Merging involves timing the flow of original andreagent drops so that they pair up and are in contact. A second strategyuses electric fields to destabilize a passing drop so it can be injectedwith reagent from a side channel. This avoids the issue ofsynchronization, but has the disadvantage that each drop is potentiallycross-contaminated when joined with the side channel. Furthermore, onlya volume less than or equal to the passing drop can be injected.

Rather than merging or injecting reagents with a drop, presented here isa different scheme where the original drop is enveloped within a largerreagent droplet and then both are coalesced via application of anelectric field. In some embodiments, this enveloping facilitates thepairing of one original drop with one reagent envelope. The containednature of the mixing may also limit cross-contamination and facilitatethe addition of arbitrary volumes as compared with a droplet injector.

The drop-envelope pairing is made possible with surface chemistry. Toreduce interfacial energy, a hydrophilic channel encapsulates anoil-coated drop in aqueous reagent if available. A subsequenthydrophobic channel then encapsulates it in oil, creating a stablewater-in-oil drop in a water-in oil drop, or triple emulsion (E3). Thistechnique of alternating channel hydrophobicity has each low-orderemulsion triggering the formation of the next higher one, with reliablequintuple emulsions even possible. The triggering leads to the properpairing of one original drop per envelope. Once there, the original dropsurface is in maximal contact with the inner surface of the reagentenvelope, facilitating later electro-coalescence. This contact meansthat any volume of reagent could be added to the original drop, from athin-shelled reagent envelope of fractional volume to an envelope 10²,10³, 10⁴ or more times larger.

A detailed schematic of the E3 scheme is shown in FIG. 23. First, apremade, water-in-oil emulsion (E1) was reinjected into the devicethrough a hydrophilic channel (FIG. 23, top left). The drops met ajunction where co-flowing reagent pinched them off individually,surrounding them to reduce surface repulsion. The oil of the E1 formedthin, stable shells that housed each original drop. The channelimmediately after the junction was designed to include ridges asdescribed herein to traps pockets of aqueous fluid. This prevented oilfrom contacting the walls during budding and potentially altering theirhydrophobicity. The water-in-oil-in water double emulsion (E2) thentraveled to a second junction where it met a hydrophobic channelcarrying oil (FIG. 23, bottom left) (Additional description andcharacterization of double emulsions and their formation are provided inthe descriptions of FIGS. 38-51). Here, the aqueous reagents wererepelled from the walls, and formed an E3 drop. In the figure, the E2 isshown in the process of seeding the E3 by weakening the adhesion of thereagent fluid to the hydrophilic channel. The volume ratio of reagent tothe original E1 drops was determined by the flow rates at the firstjunction.

After formation, the E3 was passed into a narrow constriction andcoalesced with an electric field. The electric field was generatedbetween two salt-solution containing channels, an electrode carrying ahigh, alternating voltage and a grounded moat (FIG. 23, bottom). Theconstriction may have facilitated application of the electric field tothe drops because the reagent envelope likely contained mobile ions thatcould screen the interior from the electric field. As seen in thefigure, constricting the E3 forces the inner drop to the channel wall.After coalescing, the oil shell collapsed and became the innermost phaseof an inverted oil-water-oil double emulsion (E2′).

The device itself was constructed using conventional PDMS fabricationtechniques. First, a master was made by spinning layers of SU-8 resistonto a silicon wafer and sequentially exposing them with UV light(Blakray) and a patterned mylar mask (Fineline Imaging) After developingin CD-30, the SU-8 master was covered in PDMS (PDMS manufacturer) with a10:1 polymer to cross-linker mix, placed in vacuum to remove trappedair, and baked for 1 hour at 75° C. The device was then extricated andgiven access holes with a 0.75 mm biopsy punch. Next, the device wasbonded to a 1 mm-thick glass slide by exposing both to 1 mbar O₂ in a300 W plasma cleaner for 20s, attaching, and then baking for 10 min at75° C.

The final processing steps created the hydrophilic and hydrophobicchannels. First, Aquapel® was flowed backwards through the device, intothe drop outlet and out the carrier oil inlet. At the same time, thedrop reinjector inlet was pressurized with 15 psi air to prevent theAquapel® from entering the double-emulsion, hydrophilic section of thedevice. Next, the same inlets exposed to Aquapel® were plugged with PEEKtubing (Resolution Systems, TPK.515-5M) and the device was re-exposed to1 mbar O₂ plasma in the same cleaner for 1 min. The plasma made exposedchannels hydrophilic, while the plugs kept the hydrophobic channels asthey were. This hydrophilic treatment was only semi-permanent, and othermethods not used here are capable of creating robust hydrophilicchannels.

To operate, syringes filled with the appropriate fluids were connectedto the finished device via PE-2 tubing (Scientific Commodities,#BB31695) and the same PEEK tubing and pressurized using syringe pumps(New Era). The reinjected drops consisted of Milli-Q water in afluorinated oil (Novec HFE 7500) with a 1% w/w biocompatiablesurfactant. The drops were flowed at a relatively slow flow rate of 20μL/hr, and a snaking channel was used (FIG. 23, top left) to add flowresistance and filter any pressure fluctuations. The test reagent wasPBS buffer (model #) with 0.1% pluronic surfactant (model #), and thecarrier oil was the same as with the reinjected drops. These were flowedat equal rates between 200 μL/hr and 1200 μL/hr. The electrodes and moatwere filled with 3.0 NaCl solution. The electrode, which was a dead end,was pressurized with a solution-filled syringe until air in the channelwas absorbed by the PDMS. It was connected to a 20 kHz high voltageoscillator (JKL Components Corp, BXA-12579) running at 500 V. Such largevoltages applied to merge or inject drops have been shown to bebiologically compatible.

FIG. 24 shows microscope images of the running E3 device. The reinjectedE1 travelling from the top of FIG. 24, Panel A, are starkly outlinedbecause the disparate oil and water indices of refraction bent the backlighting. After the E1 was encapsulated at the junction by reagentflowing from the sides and became an E2, the inner and outer indices ofrefraction matched and the borders became much fainter. This is anindication of the thinness of the oil shell, which did not appreciablyrefract. In FIG. 24, Panel A, the E1 consisted of 30 μm-diameter drops(15 pL), and all channels here were hydrophilic and square, 30 μm to aside.

At the next junction, seen in FIG. 24, Panel B, the E2 exited thehydrophilic channel as an E3 in a large square, hydrophobic channel, 60μm to a side. As with the initial emulsion, the edges of these E3 dropswere clearly visible due to refractive mismatch. Conceivably, this stepcould have caused timing issues because the inner E1 needed tosynchronize with the large drop formation. However, this problem wasavoided because the arrival of the E1 at the junction weakened theadhesion of the reagent phase to the hydrophilic channel and inducedbudding. The process is shown in the inset of FIG. 24, Panel B, andcaused a very regular loading of E1 into the E3.

The coalescence of the E3 is shown in FIG. 24, Panel C. The 60 μm-widechannel narrowed to 15 nm, squeezing the E1 against the walls where theelectric field from the electrode could penetrate. The new E2′ productof coalescing can be seen on the right. The collapsed oil remnantsappear in high contrast and have a volume of roughly 2 pL, correspondingto an original oil shell that was 1 nm thick. The remnants couldconceivably have merged with the carrier oil during coalescence exceptfor the fact that the E3 was squeezed against the channel wall wherethere is no oil. In the inset, the constriction is shown withoutelectric field. No coalescence occurred and the constriction moved theinner phases to the rear. The regularity of coalescence is demonstratedin FIG. 24, Panel D, the top of which shows a mixing channel forhomogenizing the aqueous contents of the drop.

The precise dynamics of E3 coalescing were determined using a fastcamera. Two time series are shown in FIG. 25, with the oil shell of theinner E1 highlighted in blue (indicated by arrows in FIG. 25). Eachstarts out at a time t=−0.7 ms where the inner E1 was not yetconstricted and was spherical. Time t=0.0 ms was set immediately beforerupturing when the E1 was pinned against the constriction walls andslightly flattened. By next frame, t=0.1 ms, the E1 ruptured. In FIG.25, Panel A, the rupturing ejected contents of the E1 to the back of thedrop, whereas in FIG. 25, Panel B, the contents were ejected forward. Inhigh-order emulsions, the unconstrained surface of an inner phase willbe tangent somewhere with the surface of the next outermost phase toreduce interfacial energy (i.e. the phases are never perfectlyconcentric). This randomly positioned contact point helps merging andmay determine where the drop ruptures. After rupturing, the oil shellscollapsed as shown in the frame at t=1.1 ms.

The robustness of this process depends on the appropriate channels beinghydrophilic or hydrophobic. If the first section of the device is notsufficiently hydrophilic, the oil of E1 may wet the channel wallsimmediately after the junction. Instead of travelling as spheres downthe center of the channel as in FIG. 24, Panel A, they may travel ashemispheres down the side and slip into the carrier fluid at the nextjunction as a single emulsion rather than enveloped. If the secondsection of the device is not sufficiently hydrophobic, there may beelectro-wetting at the constriction and small satellite drops will buffoff at the tail of the passing E3. As is, this scheme produces aqueousdrops with oil in them (E2′) as opposed to the pure aqueous drops (E1)of the merger and injector strategies mentioned previously. Depending onthe desired product, this might be acceptable; otherwise, varioustechniques like microfluidic centrifuges or drop splitting can beemployed to remove the oil.

From the study described, a triple emulsion coalescence strategy wasdemonstrated to be a robust method for adding a reagent to a collectionof drops. Such triple emulsion coalescence was carried out without lossof drops or drop mixing, owing to the surface chemistry of the channelsrather than careful synchronization.

Example 5: Picoinjection Enables Digital Detection of RNA Molecules withDroplet RT-PCR

Most biological assays require the stepwise addition of reagents atdifferent times. For microfluidic techniques to be most widely useful, arobust procedure for adding reagents to drops is therefore important.One technique for accomplishing this is electrocoalescence of drops, inwhich the reagent is added by merging the drop with a drop of thereagent using an electric field. Another technique is picoinjection,which injects the reagent directly into the drops by flowing them past apressurized channel and applying an electric field. An advantage ofpicoinjection is that it does not require the synchronization of twostreams of drops, making it easier to implement and more robust inoperation. However, variability in the volume injected from drop to dropand the potential degradation of reagents by the electric field mayinterfere with assays. In addition, during picoinjection, the dropstemporarily merge with the reagent fluid, potentially allowing transferof material between drops, and cross-contamination.

This study investigated the impact of picoinjection on biological assaysperformed in drops and the extent of material transfer between drops.Using sensitive digital RT-PCR assays, it is shown that picoinjection isa robust method for adding reagents to drops, allowing the detection ofRNA transcripts at rates comparable to reactions not incorporatingpicoinjection. It was also determined that there is negligible transferof material between drops. The benefit of workflows incorporatingpicoinjection over those that do not is that picoinjection allowsreagents to be added in a stepwise fashion, opening up new possibilitiesfor applying digital RT-PCR to the analysis of heterogeneous populationsof nucleic acids, viruses, and cells.

Materials and Methods

Microfluidic Device Fabrication

The microfluidic devices consisted of polydimethylsiloxane (PDMS)channels bonded to a glass slide. To make the PDMS mold, a device masterwas first created by spinning a 30 mm-thick layer of photoresist (SU-83025) onto a silicon wafer, followed by a patterned UV exposure andresist development. Next, an uncured mix of polymer and crosslinker(10:1) was poured over the master and baked at 80° C. for 1 hour. Afterpeeling off the cured mold, access holes were punched in the PDMS slabwith a 0.75 mm biopsy coring needle. The device was washed withisopropanol, dried with air, and then bonded to a glass slide followinga 20 s treatment of 1 mbar O₂ plasma in a 300 W plasma cleaner. To makethe devices hydrophobic, the channels were flushed with Aquapel® andbaked at 80° C. for 10 min.

RNA Isolation

Human PC3 prostate cancer or Raji B-lymphocyte cell lines were culturedin appropriate growth medium supplemented with 10% FBS, penicillin andstreptomycin at 37° C. with 5% CO₂. Prior to RNA isolation, Raji cellswere pelleted and washed once in phosphate buffered saline (PBS).Confluent and adhered PC3 cells were first trypsinized prior topelleting and washing. Total RNA was isolated from cell pellets using anRNeasy Mini Kit (Qiagen). Total RNA was quantified using aspectrophotometer and the indicated amounts (between 150 and 1000 ng) ofRNA were used in subsequent 25 ml RT-PCR reactions.

TaqMan® RT-PCR Reactions

The sequence of amplification primers used for the RT-PCR reactions wereas follows: EpCAM Forward 5′-CCTATGCATCTCACCCATCTC-3′ (SEQ ID NO:1),EpCAM Reverse 5′-AGTTGTTGCTGGAATTGTTGTG-3′ (SEQ ID NO:2); CD44 Forward5′-ACGGTTAACAATAGTTATGGTAATTGG-3′ (SEQ ID NO:3), CD44 Reverse5′-CAACACCTCCCAGTATGACAC-3′ (SEQ ID NO:4); PTPRC/CD45 Forward5′-CCATATGTTTGCTTTCCTTCTCC-3′ (SEQ ID NO:5), PTPRC/CD45 Reverse5′-TGGTGACTTTTGGCAGATGA-3′ (SEQ ID NO:6). All PCR primers were validatedprior to use in microfluidic droplet experiments with tube-based RT-PCRreactions. Products from these reactions were run on agarose gels andsingle bands of the predicted amplicon size were observed for eachprimer set. The sequence of the TaqMan® probes was as follows: EpCAM5′-/6-FAM/ATCTCAGCC/ZEN/TTCTCATACTTTGCCATTCTC/IABkFQ/-3′ (SEQ ID NO:7);CD44 5′-/Cy5/TGCTTCAATGCTTCAGCTCCACCT/IAbRQSp/-3′ (SEQ ID NO:8);PTPRC/CD45 5′-/HEX/CCTGGTCTC/ZEN/CATGTTTCAGTTCTGTCA/IABkFQ/-3′ (SEQ IDNO:9). Pre-mixed amplification primers and TaqMan® probes were orderedas a PrimeTime Standard qPCR assay from Integrated DNA Technologies(IDT) and were used at the suggested 1× working concentration.Superscript III reverse transcriptase (Invitrogen) was added directly toPCR reactions to enable first stand cDNA synthesis. Followingemulsification or picoinjection of RT-PCR reagents, drops were collectedin PCR tubes and transferred to a T100 Thermal Cycler (BioRad).Reactions were incubated at 50° C. for 15 min followed by 93° C. for 2min and 41 cycles of: 92° C., 15 s and 60° C., 1 min.

Emulsion Generation and Picoinjection

The reaction mixtures were loaded into 1 mL syringes and injected intomicrofluidic T junction drop makers using syringe pumps (New Era)controlled with custom LabVIEW software. The dimensions of the deviceand flow rates of the reagents were adjusted to obtain the desired 30 mmdrop size. To apply the electric field for picoinjection, the electrodeand surrounding moat channels were filled with a 3M NaCl solution,having a conductivity of ˜0.1 S/cm. The electrode was energized using 20kHz, 300 VAC signals generated by a fluorescent light inverter (JKLComponents Corp) attached via an alligator clip to the syringe needle.

Immunofluorescence Imaging

To image the thermocycled droplets, 10 mL of emulsion were pipetted intoCountess chambered coverglass slides (Invitrogen). The slides wereimaged on a Nikon Eclipse Ti inverted microscope using conventionalwidefield epifluorescence and a 4× objective. Fluorescence filters werechosen to optimize the signal intensity and to mitigate backgroundfluorescence due to spectral overlapping of the dyes used in themultiplexed reactions. The images were captured using NIS Elementsimaging software from Nikon.

Data Analysis

The droplet images were analyzed using custom MATLAB software. For eachfield of view, brightfield and fluorescence images were captured. Thesoftware first located all drops in the brightfield image by fittingcircles to the drop interfaces. Next, the light background in thefluorescence images was subtracted using a smooth polynomial surfaceconstrained to vary over size scales much larger than the drops. Thesoftware then measured the average fluorescence intensity within eachdroplet's circular boundary. The resultant intensity values were offsetso that the cluster of lowest intensity (empty) had an average of zero.Drops were determined to be “positive” or “negative” based on whethertheir intensity fell above or below, respectively, a defined threshold.

Results

Detection of RNA Transcripts in Picoinjected Drops.

A potential concern when using picoinjection for RT-PCR assays is thepossibility that it may interfere with reactions in the drops; forexample, the process may result in variability in the amount of reagentsbetween the drops or degradation of key components upon exposure to theelectric field. To investigate these issues, the detection of twocancer-relevant human transcripts, EpCAM and CD44, was compared inpicoinjected and non-picoinjected drops using TaqMan® RT-PCR, (FIG. 26).The TaqMan® probe for detecting EpCAM was conjugated to the fluorophore6 carboxyfuoroscein (FAM) and the probe for CD44 to the dye Cy5. Theprobe mix also contained primers that flank the TaqMan® probes and yield˜150 base amplicons from these genes.

To prepare the non-picoinjected control drops, the probe mix was addedto a 25 ml RT-PCR master mix reaction containing 150 ng of total RNAisolated from the human PC3 prostate cancer cell line. The RT-PCRsolution was the emulsified into monodisperse 30 mm (14 pL) drops with aT-junction drop maker, and the drops were collected into PCR tubes andthermocycled (FIG. 26, Panel A and 26, Panel C). During thermocycling,drops containing at least one EpCAM or CD44 transcript were amplified,becoming fluorescent at the wavelengths of the associated FAM and Cy5dyes. By contrast, drops without a molecule did not undergoamplification and remained dim, as in standard TaqMan®-based digitaldroplet RT-PCR. Following thermocycling, the drops were pipetted intochambered slides and imaged with a fluorescence microscope. To measurethe concentrations of EpCAM and CD44 in the original solution, thenumber of drops with FAM or Cy5 fluorescence were counted. The reactionsshowed a digital fluorescent signal for both the EpCAM and CD44 probes,indicating that these transcripts were present at limitingconcentrations in the drops, as shown in FIG. 27, Panel A. Controlreactions where reverse transcriptase was omitted failed to produce afluorescent signal, indicating that the TaqMan® assays were specific andnot the result of non-specific cleavage of TaqMan® probes caused by theemulsification process.

To test the impact of picoinjection on TaqMan® RT-PCR, a similarexperiment as above was performed, but the RT-PCR reagents wereseparated into two solutions added at different times. Total RNA, RT-PCRbuffer, primers, probes, and DNA polymerase were emulsified into 30 mmdiameter drops; these drops were not capable of RT-PCR, since theylacked reverse transcriptase. Using picoinjection, an equal volume of 2×reverse transcriptase was introduced in PCR buffer and the drops werethermocycled. Just as with the non-picoinjected control, this emulsionshowed a robust digital signal and had an equivalent ratio offluorescent-to-non-fluorescent drops, as shown in FIG. 27, Panels A andB. To confirm that the fluorescence was not due to background hydrolysisof the TaqMan® probes, disruption of the probes by the electric field,or some other factor, additional reactions were performed where apicoinjection fluid lacking reverse transcriptase was added toRNA-containing drops. In these drops, no fluorescence was evidentfollowing thermocycling (FIG. 27, Panel C), demonstrating that thesignal was indeed a result of digital detection of RNA molecules, andthat these assays were specific.

Quantification of RT-PCR Detection Rates in Picoinjected Drops

To precisely quantify the impact of picoinjection on TaqMan® RT-PCRtranscript detection, four independent replicates of the picoinjectedand non-picoinjected drops were collected. To automate data analysis, acustom MATLAB software was used to locate the drops in the images andmeasure their fluorescence intensities. For a particular channel (FAM orCy5), the fluorescence intensity within each drop was averaged; all dropvalues were subsequently offset so that the cluster of empty drops hadan average of zero (See Materials and Methods). Using one threshold forboth channels, each drop was labeled as positive or negative for EpCAMand CD44 based on whether it was above or below the threshold,respectively, as shown in FIG. 28, Panel A. In total, 16,216 controldrops and 14,254 picoinjected drops were analyzed from the fourexperimental replicates. To determine the TaqMan® detection rate ofpicoinjected drops relative to non-picoinjected controls, the totalnumber of CD44 (Cy5) and EpCAM (FAM) positive control drops in eachreplicate was normalized. Following picoinjection of reversetranscriptase, 92% (+/−26%) of CD44 positive drops and 87% (+/−34%) ofEpCAM positive drops were detected relative to the control drops (FIG.28, Panel B). Although the average transcript detection rate forpicoinjected drops was slightly lower than that of control drops for agiven RNA concentration, the difference was not statisticallysignificant, and some experimental replicates had detection rates forpicoinjected drops higher than for the controls. Based on these results,it was conclude that picoinjection affords transcript detection ratesequivalent to that of digital RT-PCR, with the benefit of allowing thereaction components to be added at different times.

Discrete Populations of Drops can be Picoinjected with MinimalCross-Contamination

An important feature when adding reagents to drops is maintaining theunique contents of each drop and preventing the transfer of materialbetween drops. Unlike the merger of two discrete drops, the contents ofa picoinjected drop become momentarily connected with the fluid beingadded, as illustrated in FIG. 26, Panel B. After the drop disconnectsfrom the fluid, it may leave material behind that, in turn, may be addedto the drops that follow. This could lead to transfer of materialbetween drops, and cross-contamination. To examine the extent to whichpicoinjection results in cross-contamination, TaqMan® RT-PCR reactionswere again used because they are extremely sensitive and capable ofdetecting the transfer of just a single RNA molecule. A FAM-conjugatedTaqMan® probe was used for targeting the EpCAM transcript and ahexachlorofluorescein (HEX) conjugated TaqMan® probe was used forrecognizing the B-lymphocyte-specific transcript PTPRC. Total RNA wasisolated from PC3 cells expressing EpCAM but not PTPRC, and aB-lymphocyte derived cell line (Raji) expressing PTPRC but not EpCAM.For a control set of drops, the RNA from both cell types was mixed,TaqMan® probes and RT-PCR reagents were added, and the solutions wereemulsified into 30 mm drops. The drops were collected into a tube,thermocycled, and imaged, FIG. 29A. In the images, a large number ofdrops displayed FAM and HEX fluorescence, indicative of multiplexedTaqMan® detection of PTPRC and EpCAM transcripts. A smaller fraction hadpure green or red fluorescence, indicating that they originallycontained just one of these molecules, while even fewer were dim andwere thus devoid of these transcripts.

To observe the rate of picoinjector cross-contamination, a microfluidicdevice was used that synchronously produced two populations of dropsfrom opposing T-junctions, pictured in FIG. 29, Panel B. One populationcontained only Raji cell RNA and PTPRC transcripts; the other, only PC3cell RNA and EpCAM transcripts, as illustrated in FIG. 29, Panel B. Bothpopulations contained primers and TaqMan® probes for EpCAM and PTPRC andwere therefore capable of signalling the presence of either transcript.Immediately after formation, the drops were picoinjected with the 2×reverse transcriptase, thereby enabling first strand cDNA templatesynthesis for the TaqMan® assay, and an opportunity for contamination.If RNA was transferred between drops, some of the drops should havedisplayed a multiplexed TaqMan® signal, whereas in the absence ofcontamination, there should have been two distinct populations and nomultiplexing. In the fluorescence images, two distinct populations wereobserved, one positive for EpCAM (FAM) and the other for PTPRC (HEX),with almost no yellow multiplexed drops that would be indicative of amultiplexed signal, as shown in FIG. 29, Panel B. This demonstrated thatcross-contamination during picoinjection is rare.

To measure the precise rate of cross-contamination, automated dropletdetection software was used to analyze thousands of drops, FIG. 30,Panel A, and the results were plotted as a percentage of the totalnumber of TaqMan® positive drops, FIG. 30, Panel B. A total of 5771TaqMan® positive control drops and 7329 TaqMan® positive picoinjecteddrops were analyzed from three independent experimental replicates. Forthe control drops, in which the Raji and PC3 RNA were combined, amultiplexing rate 44% (+/−9.26) was observed. By contrast, for thepicoinjected drops, only 0.31% (+/−0.14) multiplexed drops wereobserved, as shown in FIG. 30, Panel B. Hence, with picoinjection, therewas some multiplexing, although the rate was so low it cannot be ruledout as resulting from other sources of RNA transfer, such as merger ofdrops during thermocycling or transport of RNA between dropletinterfaces.

The dual population experiments in which the drops were picoinjectedimmediately after being formed allowed for the estimation of the preciseamount of cross-contamination, but in most actual implementations ofpicoinjection for biological assays, the drops will be formed on onedevice, removed offline for incubation or thermocycling, and thenreinjected into another device for picoinjection. To demonstrate thatpicoinjection is effective for digital RT-PCR reactions performed underthese conditions, and to estimate the rate of cross contamination, adual population of drops was again created, but this time the drops werepulled offline and stored in a 1 mL syringe before reinjecting andpicoinjecting them. Just as before, it was observed that nearly alldrops were pure green or red, indicating minimal cross contamination, asshown in FIG. 31. However, some drops with a multiplexed signal werealso observed, as shown by the rare yellow drops in the image. In thisexperiment, the multiplexing rate was 1%, higher than with the dropsthat were picoinjected immediately after formation. Whilecross-contamination at the picoinjector cannot be ruled out, it issuspected that the higher multiplexing rate was the result of merger ofdrops during offline storage and reinjection, during which the drops maybe subjected to dust, air, and shear forces that can increase thechances for merger. This is supported by the observation that duringreinjection of the emulsion there were occasional large merged drops,and also that the picoinjected emulsion was somewhat polydisperse, asshown in FIG. 31. Nevertheless, even under these rough conditions, thevast majority of drops displayed no multiplexing, indicating that theyretained their integrity as distinct reactors.

From these studies, it was demonstrated that picoinjection is compatiblewith droplet digital RT-PCR and affords single RNA molecule detectionrates equivalent to workflows not incorporating picoinjection. Thisshowed that picoinjection is compatible with reactions involving commonbiological components, like nucleic acids, enzymes, buffers, and dyes.It was also observed that there was negligible transfer of materialbetween drops during picoinjection. These results support picoinjectionas a powerful and robust technique for adding reagents to drops forultrahigh-throughput biological assays.

Example 6: Single Cell RT-PCR Microfluidic Device

FIG. 32 shows one embodiment of a single cell RT-PCR microfluidic deviceas provided herein. The cells of interested were first encapsulated indrops with lysis reagent including proteases and detergents andincubated offline. These drops were then introduced into this device andspaced by oil using an input microchannel and a flow focus drop makerfor introducing microdroplets (Panel A). In a pairing microchannel, thespaced drops were then paired with large drops containing a dilutionbuffer that were created by a dilution buffer drop maker in fluidiccommunication with the pairing microchannel (Panel B). The big and smalldrops were then merged in a merging microchannel with an electric field(Panel C), adding the contents of the small drop to the large drop. Themerged drops passed through mixing microchannels and then a smallportion was sampled from them by a drop sampler (Panel D). The smallportion was then passed by a picoinjection microchannel where the smallportion was then picoinjected with the RT-PCR reagent (Panel E). Thedrops were then thermocycled for the RT-PCR reaction.

This system facilitated single cell RT-PCR because it allowed for theperformance of the cell lysis and protein digestion in one step (notshown) and subsequent dilution of the lysate in the drop prior toaddition of the RT-PCR reagent. Without the dilution, the lysate couldhave inhibited the RT-PCR reaction.

The device worked robustly, at least in part, because the timing of eachmicrofluidic component was set by the periodicity of the large dropmaker making the dilution drops. Without this periodic drop formation,the device might operate less stably and potentially producepolydisperse drops.

Example 7: Testing of Microfluidic Droplet Forming Devices UtilizingChannels Including Ridges

T-junction drop makers with and without channel ridges positioneddownstream of the T-junction were tested to determine the effect ofincluding such ridges on droplet formation performance. The channelwidths were about 30 microns and the width of the ridge peaks were fromabout 5 to about 10 microns. See FIG. 33.

PDMS microfluidic devices were prepared generally as described hereinand plasma treated for 10 seconds. The flow rate ratio was monitored,wherein the sum (Q_(sum)) of individual flow rates (Q_(oil)+(Q_(aq)) wasapproximately 1000 μl/hr, and the ratio (R)=Q_(aq)/Q_(sum), and dropletformation was visualized.

As the flow rate ratio was increased for the device lacking ridges, thedrop maker stopped forming drops and instead formed a long jet. Withoutintending to be bound by any particular theory, it is believe that thiswas due to the jet wetting the channel walls and adhering, preventingthe formation of drops. See FIG. 33, left side. For the device whichincluded the ridges, the ridges successfully trapped oil near the walls,making it difficult for the aqueous phase to wet. This allowed thedevice to form drops at much higher flow rate ratios before iteventually wet at R=0.9. This demonstrated that the ridges allow thedrop maker to function over a much wider range than would be possiblewithout the ridges. The top and bottom sets of images in FIG. 33correspond to experiments performs with different devices. When theexperiment was performed with the first pair of devices, a 21-foldincrease in maximum Q_(aq)/Q_(oil) was achieved. When the sameexperiment was performed with a second set of devices, an 8-foldincrease in maximum Q_(aq)/Q_(oil) was achieved. This discrepancy may beattributed to experimental variability because the wetting propertiesthat lead to jetting are somewhat unpredictable, hysteretic, and proneto variability.

Example 8: Fabrication and Testing of Liquid Electrodes

Many microfluidic devices utilize metal electrodes to create electricfields when such fields are called for in a particular microfluidicdevice application. However, there may be disadvantages to using suchmetal electrodes including an increased number of fabrication steps andthe potential for failure of the electrodes.

Advantageously, the present disclosure describes the fabrication and useof liquid electrodes, which simplify the fabrication process and providesimilar and/or improved capabilities relative to metal electrodes.

FIG. 34 provides an overview of an exemplary liquid electrodefabrication method. Initially, an SU-8 photoresist master was fabricatedon an Si wafer (A). PDMS was then cast, degassed and cured (B). Inletports were punched in the PDMS, and the PDMS was bonded to a glass slide(C). Finally, the channel was filled with a NaCl solution. FIG. 35provides a sequence of three images taken at different times as anelectrode channel was being filled with salt water (time course proceedsfrom left to right). The salt water was introduced into the inlet of thechannel and pressurized, causing it to slowly fill the channel. The airthat was originally in the channel was pushed into the PDMS so that, bythe end, it was entirely filled with liquid.

Electric field lines for various liquid electrode configurations weresimulated as shown in FIG. 36. The simulations are of positive andground electrodes showing equipotential lines for three differentgeometries.

The liquid electrodes were capable of merging drops through applicationof an electric field as shown in FIG. 37, which provides two images of adroplet merger device that merges large drops with small drops utilizingliquid electrodes. To merge the drops, an electric field was appliedusing a salt-water electrode. When the field was off, no merger occurred(right) and when it was on, the drops merged (left).

Example 9: PCR Analysis and FACS Sorting of Azopira/E. coli Mixture

Two different species of microbes, Azospira and E. coli. Wereencapsulated in microdrops. In-droplet PCR was performed using TaqMan®and primers for Azospira and/or E. coli. FIG. 52 provides images showingdrops in which a TaqMan® PCR reaction was performed with encapsulatedAzospira. The upper images correspond to a reaction in which a 110 bpamplicon was produced, whereas the lower images to a 147 bp amplicon.FIG. 53 shows a picture of a gel testing 16S primers for Azospira and E.coli. The gel shows the bands corresponding to the amplicons of twoTaqMan® PCR reactions, one for a 464 bp amplicon and one for a 550 bpamplicon. FIG. 54 provides a picture of a gel validating that thein-droplet PCR reactions can be multiplexed by adding multiple primersets to a sample containing bacteria. FIG. 55 shows results for anexperiment where the TaqMan® reaction had primers and probes only forAzospira, so only the drops containing one of these microbes underwentamplification and became fluorescent, while the empty drops or the oneswith E. coli remained dim. The emulsion was then encapsulated intodouble emulsions using a microfluidic device and sorted on FACS. Theplots to the right in FIG. 55 show the FACS data. The upper plot showsthe scattering cross section plotted as a function of the dropfluorescence. Based on this, a population was gated out by drawingboundaries (shown above), and this population was sorted based on thedrop intensity. The gating allowed erroneous events due to small oildrops or dust to be discarded. When looking at only the doubleemulsions, the population had two distinct peaks which corresponded tothe fluorescent and non-fluorescent drops, shown in the lower histogram.An attempt to re-amplify the amplicons created during the in-dropletPCRs was unsuccessful, potentially due to their chemical structure sincethey may contain analogue bases or due to an inhibitory effect of thecarrier oil.

Although the foregoing invention has been described in some detail byway of illustration and example for purposes of clarity ofunderstanding, it is readily apparent to those of ordinary skill in theart in light of the teachings of this disclosure that certain changesand modifications may be made thereto without departing from the spiritor scope of the appended claims.

Accordingly, the preceding merely illustrates the principles of theinvention. It will be appreciated that those skilled in the art will beable to devise various arrangements which, although not explicitlydescribed or shown herein, embody the principles of the invention andare included within its spirit and scope. Furthermore, all examples andconditional language recited herein are principally intended to aid thereader in understanding the principles of the invention being withoutlimitation to such specifically recited examples and conditions.Moreover, all statements herein reciting principles, aspects, andembodiments of the invention as well as specific examples thereof, areintended to encompass both structural and functional equivalentsthereof. Additionally, it is intended that such equivalents include bothcurrently known equivalents and equivalents developed in the future,i.e., any elements developed that perform the same function, regardlessof structure. The scope of the present invention, therefore, is notintended to be limited to the exemplary embodiments shown and describedherein. Rather, the scope and spirit of present invention is embodied bythe appended claims.

Example 10: Identification and Genetic Analysis of Cancer Cells withPCR-Activated Cell Sorting (PACS)

Prostate cancer cells were identified and sorted from a heterogeneouspopulation as described in greater detail below.

Materials and Methods

Cell Culture and Staining

Human DU145 prostate cancer and Raji B-lymphocyte cell lines werecultured in RPMI 1640 supplemented with 10% FBS, penicillin andstreptomycin at 37° C. with 5% CO2. Prior to cell staining, Raji cellswere pelleted and washed once in phosphate buffered saline (PBS).Adherent DU145 cells were trypsinized prior to pelleting and washing.Cells were stained in 1 ml Hank's balanced salt solution (HBSS) with 2μl %/1 Calcein Violet AM or Calcein Green AM for 30 minutes at roomtemperature. Following staining, cells were washed with PBS and thenresuspended in PBS that was density matched with OptiPrep solution priorto encapsulation in microfluidic droplets.

To generate cell suspensions with known ratios of cell types, cellcounting and viability analysis was performed on individual cell lines.This was done by combining a 10 aliquot of each cell type with an equalvolume of trypan blue and placing the mixture into a chamber slide. Livecell numbers were determined by reading the chamber slides with theCountess Automated Cell Counter (Invitrogen).

Fabrication and Operation of Microfluidic Devices

The poly(dimethylsiloxane) (PDMS) devices were fabricated using standardsoft lithographic techniques. Fluid flow was regulated viacomputer-controlled syringe pumps (NewEra) connected to the PDMS deviceswith polyethylene tubing. Fluorinated oil (FC40) with 5% PEG-PFPEamphiphilic block copolymer was used to generate the initialmicrodroplet emulsion. Lysis buffer (100 mM Tris pH 8.0, 2% Tween-20,proteinase K 1.5 mg/mL) was introduced at the time of cell encapsulationusing a co-flow drop maker to prevent premature rupture of cells.

Microdroplet TaqMan RT-PCR

Amplification primers for the vimentin RT-PCR reactions were as follows:Primer1 5′-GTGAATCCAGATTAGTTTCCCTCA-3′ (SEQ ID NO:10), Primer25′-CAAGACCTGCTCAATGTTAAGATG-3′ (SEQ ID NO:11); The sequence of thevimentin TaqMan probe was: 5′-HEX/CGCCTTCCA/ZEN/GCAGCTTCCTGTA/IABkFQ-3′(SEQ ID NO:12). TaqMan reaction primers and probes were purchased as apre-mixed assay from Integrated DNA Technologies (IDT). Superscript IIIreverse transcriptase and Platinum Taq DNA polymerase (Invitrogen) wereused for the microdroplet single-cell TaqMan reactions. Thermocyclingconditions were 50° C. for 15 min followed by 93° C. for 2 min and 45cycles of: 92° C., 15 s and 60° C., 1 min. Thermocycled droplets wereeither imaged on a fluorescent microscope to confirm specificity ofTaqMan reactions or transferred to a 1 ml syringe and reinjected into amicrofluidic droplet sorter.

Ultrahigh-Throughput Detection and Sorting of Droplets

Droplets were sorted dielectrophoretically using custom LabVIEW codecontrolling an FPGA card (National Instruments). Two lasers (405 and 532nm) were focused onto the channel upstream of the sorting junction,allowing the droplets to be scanned for fluorescence. The FPGA cardanalyzed the emitted fluorescence measured with spectrally-filtered PMTs(Hamamatsu Photonics) and outputted a train of 1 kV, 30 kHz pulses tothe microfluidic electrode via a high voltage amplifier (Trek) to directappropriate droplets into a collection channel. Droplets that had mergedprior to sorting were measurably large and automatically discarded.During detection, the average HEX and calcein violet fluorescence ofeach droplet were recorded and plotted with MATLAB code. To quantifysorting efficiency, sorted droplets were analyzed with MATLAB code whichidentified droplets based on their circular boundary in brightfieldimages and then measured their fluorescence in the associatedepifluorescence images.

DNA Sequencing of PACS-Sorted Genomic DNA

Following collection of sorted droplets, emulsions were broken usingperfluoro-1-octanol and the aqueous fraction was diluted in 10 mM TrispH 8.0. The aqueous layer containing the pooled cellular lysate was thenpurified using a DNeasy Blood and Tissue Kit (Qiagen). CDKN2A and RB1were PCR amplified from gDNA isolated from both pre-sorted and vimentinsorted emulsions. Amplicons were analyzed on agarose gels and extractedwith a Qiagen Gel Extraction kit. 50 ng of gel extracted DNA was sentfor Sanger sequencing and the data was analyzed on 4Peaks sequencing andchromatogram analysis software.

For next-generation sequencing, 1 ng of each amplicon was subsequentlyused for sequencing library preparation using the Nextera XT library kit(Illumina). Sequencing was done on a HiSeq2500 sequencer with 50 bpreads. Each library was indexed with a barcode and reads wereautomatically partitioned post sequencing. Next-generation sequenceanalysis was performed using the Galaxy web-based platform. The workflowconsisted of quality checking sequence data with FASTQ Groomer, mappingthe data to a reference sequence with Bowtie, converting the mapped datato a SAM file and then generating a pileup of the sequence data. Pileupdata was analyzed for the presence of Raji or DU145-specific SNPs at therelevant positions. More than 15,000 base reads were analyzed for RB1and CDKN2A SNP positions from both the pre-sorted and vimentin-positivePACS amplicon libraries.

Quantitative RT-PCR Analysis of PACS-Sorted RNA

After breaking the emulsions with perfluoro-1-octanol, aqueous fractionsfrom the droplets were collected and purified on an RNA binding column(Qiagen). Following elution, the extracted RNA was analyzed with TaqManRT-PCR assays (Integrated DNA Technologies). Amplification reagents werefrom the SuperscriptIII One-Step RT-PCR System (Invitrogen). Threereplicates were performed for each reaction and GAPDH was used to verifythat equal amounts of RNA were used in each of the CD9 reactions.Quantitative reactions were carried out using an MX3005p Real-Time PCRSystem (Stratagene). Normalized fluorescence values from the instrumentwere plotted using Prism software. For control reactions, total RNA wasfirst isolated from Raji and DU145 cell lines using an RNeasypurification kit (Qiagen). 80 ng of total RNA was used as template foreach qRT-PCR reaction. Differences in expression levels were calculatedusing normalized Ct values obtained from the amplification plots.

Results

PACS Workflow

Factors weighing against the effective sorting of cells using TaqMan PCRas an assay readout include both the difficulty of preparing andhandling stable, single-cell containing droplets and alsolysate-mediated inhibition of the reaction in subnanoliter volumes.Development of a robust microfluidic workflow that maintainscompartmentalization of single-cell lysates at all times while alsoovercoming mammalian cell lysate-mediated inhibition of PCR hascontributed to the PACS method described herein. Cells are firstencapsulated in aqueous droplets with Tween-20 and proteinase K lysisreagents (FIG. 56, Panels A and B). The compartmentalized lysates ofsingle cells are then diluted by droplet merger and TaqMan RT-PCRreagents added by droplet picoinjection (FIG. 56, Panel C). Thedroplets, now prepared for efficient, uninhibited single-cell TaqManRT-PCR, are collected and thermocycled for amplification to identifycells expressing target transcripts. This technique has been used toachieve a single-cell RT-PCR throughput of 47,000 mammalian cells.Additionally, this approach is highly specific, enabling the unambiguousdetection of Raji cells in a mixed suspension containing PC3 cancercells. To enable lysate recovery of cells positive for the nucleic acidbiomarker, sorting of the microfluidic droplets was implemented based onthe presence of the fluorescent signal produced from the TaqMan reaction(FIG. 56, Panel D). TaqMan positive droplets containing cell lysate ofinterest are then collected and the nucleic acids extracted fordownstream sequencing.

Vimentin-Based Prostate Cancer Cell Detection

TaqMan PCR assays offer single molecule sensitivity and can be preciselytargeted to a wide variety of gene transcripts, making them ideal fordistinguishing between and sorting cells. To demonstrate the utility ofPACS-based TaqMan PCR to identify specific cells in a heterogeneouspopulation, expression of vimentin was targeted in DU145 prostate cancercells spiked into Raji B-lymphocyte-derived cells. Vimentin is anintermediate filament protein known to participate inepithelial-to-mesenchymal transitions and can serve as a biomarker forsome cancer cell types. It is robustly expressed in DU145 cells, but notin Raji cells. The Raji cells thus serve as both an essential controlfor the specificity of the TaqMan reactions and as a more abundant“background” cell type to assess the effectiveness of PACS enrichment ofDU145 cells.

To measure the specificity and detection rate of PACS sorting based onvimentin expression, DU145 cells were labeled with calcein violet andRaji cells with calcein green viability stains. The vimentin TaqManprobe was labeled with HEX fluorescent dye having minimal spectraloverlap with the calcein dyes. This three-color detection strategyenabled the correlation of vimentin mRNA detection with the presence ofa specific cell type, and thereby measurement of the rate at whichdroplet TaqMan PCR was able to correctly distinguish between cells.

Calcein-labeled DU145 and Raji cells were mixed in roughly equal ratiosand encapsulated in droplets for lysis. The droplets were then processedon the disclosed microfluidic system to prepare them for RT-PCR and addTaqMan reagents. Following droplet collection and thermocycling, thedroplets were imaged on a fluorescence microscope to measure theintensities of the channels corresponding to the calcein dyes and HEXTaqMan probe (FIG. 57, Panel a). The images were subsequently analyzedusing a custom MATLAB script to measure the correlation between the twocalcein dyes and the TaqMan probe signal (FIG. 58, Panels a-d). Thisenabled determination of the percentage of Raji and DU145 cells detectedwith the vimentin TaqMan reaction (FIG. 57, Panel b). The detection ratefor DU145 cells was 82.3% (+/−15.1) and for Raji cells 3.4% (+/−1.0).Although a low percentage of Raji cells appear to be vimentin-positive,correlation analysis between calcein violet and green cell stainsindicates that the majority of these events occur from both Raji andDU145 cells being in the same droplet during cell encapsulation, aresult of random Poisson loading (FIG. 58, Panels a-d). The ability todetect multiple transcript types in Raji cells with high efficiency hasbeen demonstrated, indicating that the extremely low number of Rajicells determined to express vimentin is not an artifact of reducedRT-PCR efficiency in the presence of Raji cell lysate. Together, theseresults demonstrate that vimentin expression is a specific biomarker forDU145 cells compared to Raji cells, and that by interrogating forvimentin it will be possible to identify and recover these cells out ofa heterogeneous population.

Enrichment of DU145 Cells Out of a Mixed Population with PCR-ActivatedCell Sorting

In addition to detecting cells based on nucleic acid analysis, in someembodiments, one of the goals of PACS is to recover the lysates of thepositive cells. To demonstrate this capability, another sample wasprepared in which DU145 cells were spiked into Raji cells at 20% and80%, respectively. The cells were then labeled with calcein violet,which acted as a fluorescent indicator for droplets that originallycontained a live cell; this internal control allows for theidentification of false positive droplets undergoing amplification dueto the presence of vimentin transcripts but that did not contain asingle cell (“digital background”). Following staining, cells wereencapsulated, lysed, and run through the PCR addition device, taking ˜4hours. The droplets were collected, thermocycled, stored overnight at 4°C., and sorted the following day. During sorting, droplets containingcell lysates positive for vimentin expression were recovered by gating.This was accomplished by discarding all droplets which were below thegating thresholds for either the HEX or calcein signals (uncolored, FIG.59, Panel a) and recovering all droplets above the thresholds for bothsignals (pseudo-colored purple, FIG. 59, Panel a).

During sorting, statistics were collected on droplet fluorescence. Ascatter plot of HEX versus calcein fluorescence reveals that over132,000 single cells were interrogated and over 1.2 million dropletRT-PCRs were performed, FIG. 59, Panel b. The dashed red lines demarcatethe sorting thresholds used to recover positive droplets. Of dropletscontaining cell lysate, 16.4% were also positive for TaqMan fluorescence(upper-right quadrant, FIG. 59, Panel b). This measured value is in goodagreement with the number of DU145 cells expected (16.5%) based on thecontrolled spike-in value (20%) and the detection rate independentlymeasured in the previous experiment (82.3%, FIG. 57, Panel b). A smallfraction of droplets were devoid of calcein stain but neverthelessexhibited TaqMan signal. We have observed and reported this previouslyand attribute it to free vimentin transcripts released into suspensionduring cell encapsulation, which is likely due to inevitable cell deathduring this step 8. These “digital background” droplets are discarded bythe sorter, since they fall below the cell stain threshold (verticaldashed line, FIG. 59, Panel b).

To confirm the function of the sorter and appropriate selection ofsorting gates, the sorted droplets and a small portion of the originalpre-sorted emulsion were examined (FIG. 59, Panel c). A scatterplot ofthe HEX and calcein fluorescence values revealed that 95.8% ofpositively-sorted droplets had significant calcein and HEX fluorescence(FIG. 60). Conversely, only 0.9% of pre-sorted droplets were positivefor both signals. This constitutes a more than 100-fold increase in thedouble-positive droplet ratio following sorting, and confirms theability of PACS to enrich specific cells from a heterogeneouspopulation.

Genetic Analysis of PACS-Sorted Cancer Cells

A major advantage of PACS over FISH-FC is that it does not requirechemical fixation, enabling facile analysis of nucleic acids recoveredwith sorting. To more thoroughly characterize the ability of PACS tospecifically sort target cells out of a heterogeneous population andsequence the recovered material, a suspension containing 10% DU145 and90% Raji cells was sorted. DU145 cells have genetic mutations in twocommonly mutated tumor suppressor genes, RB1 and CDKN2A, which likelycontribute to the transformation of this prostate cancer cell line.These two mutations are homozygous SNPs residing at genetically unlinkedgenomic loci and are not found in Raji cells (upper panels, FIG. 61,Panels a-b); consequently, they represent clear genetic biomarkers withwhich to estimate the fraction of DU145 and Raji DNA in the recoveredmaterial.

In this experiment, 92,996 individual cells were analyzed, of which10.8% (10,099) were positive for vimentin and cell stain. To perform thegenomic analysis, DNA was isolated from the pre- and post-sortedemulsions. Purified genomic DNA from a total of 1,326 (˜13% of totaldroplets positively sorted) was used to amplify RB1 and CDKN2A, and theSNP regions for both genes were analyzed by Sanger sequencing (FIG. 61).In the pre-sorted emulsion, both RB1 and CDKN2A contain Raji SNPsequences and only a weak DU145-specific nucleotide peak, reflecting therelatively minor (10%) contribution of DU145 DNA in this emulsion. Bycontrast, after sorting, sequences associated with DU145 cells dominate,with only trace Raji sequences still present, as illustrated in FIG. 61,Panels a-b, lower chromatograms. This shows that PACS can identify thegenotype of an initially undetectable cancer cell population by sortingthe heterogeneous cells based on expression of a cancer-associated gene.

The Sanger sequencing chromatograms provided a measurement of DU145enrichment. In addition, next-generation sequencing was performed tomeasure the exact proportion of SNPs associated with the two differentcell types in the sorted pool. Nextera libraries were generated from theRB1 and CDKN2A amplicons obtained in the previous experiment. Followingnext-generation sequencing, the percentage of reads containing SNPs weremeasured from the two different cell types (FIG. 62, Panels a-b). In thepre-sorted emulsion, for RB1, DU145-specific codons made up 6.2% of thetotal reads. Following vimentin-positive PACS, this codon variant was87.7% of all reads. Similar results were obtained for the CDKN2A locus,with DU145 codons accounting for 13.5% of total reads pre-sorting and74.2% post-sorting. The differences between the RB1 and CDKN2Apercentages may be due to bias introduced during sequencing librarypreparation with Nextera and PCR. These results are consistent with theexpected SNP percentages in the original 10% DU145 and 90% Raji cellsuspension, and provide a quantitative validation of successfulenrichment of DU145 cells with PACS.

Gene Expression Analysis of PACS-Sorted Cells

RNA recovered from vimentin-positive droplets for the enrichment oftranscripts differentially expressed in DU145 cells compared to Rajicells were examined to investigate the ability of PACS to enabledownstream gene expression analysis of sorted cells. Analysis of controlRNA isolated from individual Raji and DU145 cells demonstrated that CD9expression is more than 16,000 times higher in DU145 cells than in Rajicells when normalized to GAPDH expression (FIG. 63, Panel a). Followingvimentin-positive PACS on the DU145 and Raji cell suspension, RNArecovered from 4,659 TaqMan sorted droplets was divided and used forGAPDH and CD9 qRT-PCR replicates (FIG. 63, Panel b). RNA input forpre-sorted and PACS sorted samples were normalized with GAPDH controls.CD9 was detected in PACS sorted droplets and absent from the pre-sortedemulsion. This indicates that downstream gene expression analysis onlysates recovered with PACS is feasible. An additional benefit of PACSis that it can use RT-PCR to detect the cell types of interest;implementation of first strand cDNA synthesis in this step facilitatespan-transcriptome analysis, including with RNA-Seq and microarrays.

The above results demonstrate the preparation of single-cell lysates forRT-PCR in microfluidic droplets and the use of TaqMan reactions forsorting. The use of single-cell TaqMan reactions not only providedspecific and sensitive detection of cells, but is also compatible withmultiplexing and analyzing non-coding RNAs, transcript splice variants,genetic mutations and other nucleic acid biomarkers undetectable withantibodies.

The results above show that embodiments of the present disclosureprovide for analysis of single cells with RT-PCR high throughput. Asdiscussed above, RT-PCR analysis and sorting of 132,000 cells wasdemonstrated in a single experiment. Likewise, scalability wasdemonstrated where certain instances showed at least a ten-fold increasein single-cell throughput. A throughput of >100,000 cells per experimentshowed that PACS provided for analysis of heterogeneous cellpopulations, including immune cells, large tumors, and even circulatingtumor and fetal cells, especially when combined with cell pre-enrichmentor depletion strategies. In certain instances, antibody fluorescence atthe time of encapsulation was used to sort cells with PACS.

As demonstrated above, PACS can be used to recover nucleic acids fordownstream analysis. The genomes of PACS-sorted cells can be sequencedin a targeted fashion and as can whole genome sequencing with theimplementation of appropriate library preparation steps downstream. PACScan be used to identify and enumerate cells based on many differentnucleic acid biomarkers for a given behaviour or cell state and cansubsequently be used to study the genetic drivers behind that behaviour.In addition to genomic analysis, PACS-recovered cells can be analyzed ingene expression analysis, which is important to the investigation ofregulatory networks and effector proteins behind cell states andbehaviour.

Example 11: PCR-Activated Cell Sorting (PACS) for Cultivation-FreeEnrichment and Sequencing of Rare Microbes

The use of PACS for the cultivation-free enrichment of rare microbes isdescribed in greater detail below. In this example, microbes from adiverse ecosystem are individually encapsulated in picoliter-volumeaqueous droplets and subjected to TaqMan PCR, followed by interrogationfor the presence of specific nucleic acid sequences. If the sequencesare present, TaqMan amplification yields a bright fluorescent signalthat fills the droplet encapsulating the cell, allowing for the recoveryof the cell's whole genome by sorting the entire droplet.

Materials and Methods

Microfabrication of Devices

Fluidic chips were fabricated using standard photolithography techniquesin poly(dimethylsiloxane) (PDMS). To produce a master, a layer of SU-8photoresist (Microchem) was first spun onto a silicon wafer, and thenexposed to UV light from a Blakray device under a mylar mask (FinelineImaging) The wafer was then baked at 95° C. on a hotplate for 1 min andthen developed in Propylene glycol monomethyl ether acetate (PGMEA). ThePDMS polymer was poured and crosslinker mixed in a 11:1 ratio over themaster and then baked at 75° C. for 4 hours. The device was then peeledfrom the master and holes were punched using a 0.75 mm biopsy coringneedle. After that, the device was bonded to a glass slide followingoxygen plasma treatment. To make the device channels hydrophobic,Aquapel was flushed into the channels, after which the device was bakedin an oven for 20 mins at 65° C. For the devices (DEP and flow focusing)in this example, the thickness of the photoresist was maintained at 25μm while the channel widths at the flow-focusing junctions were 20 μm.

Bacterial Strain Construction and Growth

The parental wild type strain was BW25113. The entire 1poA ORF wasdeleted and replaced with a sacB-cat cassette using lambda Redrecombinase-mediated allelic exchange. The Red recombinase was expressedusing plasmid pKD46. The sacB-cat cassette was generated by PCR usingplasmid pDS132 as template and primers ANG188 and ANG189. Transformantswere selected on LB Cam10 and verified by diagnostic PCR.

Next, the mutant 1poA allele was generated by two-step overlap-extensionPCR. The first-round PCR products were generated using primers ANG065and AG4 together with AG3 and ANG066, with BW25113 genomic DNA astemplate. The PCR products were treated with DpnI and gel-purified toget rid of the initial template DNA. The final PCR product was generatedusing primers ANG065 and ANG066, with the first-round PCR products astemplate (present in equimolar amounts). This PCR product was used toreplace the sacB-cat cassette as above, with selection on LB 0% NaCl 7%(w/v) sucrose. The sacB gene confers sucrose sensitivity, allowingcounterselection. Transformants were screened for chloramphenicolsensitivity (indicating loss of cassette) and verified by diagnostic PCRand sequencing. The strain produced is the LpoA K168A E. coli.

A ΔtolA::kan insertion was introduced into wild type strain BW25113 bysequential P1 transductions, with selection on LB with 10 mM sodiumcitrate and ampicillin at 50 μgml⁻¹, and LB with 10 mM Na citrate andkanamycin at 30 μgml⁻¹, respectively. The ΔtolA::kan allele is from theKeio collection E. coli gene knock-out library. The strain produced hasTolA knocked out but with a wild-type copy of the BW25113 LpoA gene.

The bacteria were grown in 2% Luria-Bertani (LB) broth at 37° C. foraround 10 hours. The bacterial cultures were then assayed for theiroptical density (OD) via spectrophotometrical measurement of absorptionat 600 nm. The correlation between OD and bacterial number is taken tobe that 1 OD is equivalent to 5×10⁸ bacteria.

Primer Sequences for the Construction of Mutant Bacterial Strains

The primer sequences used for the construction of the bacterial strainswere as follows: ANG1885′-TGCCGATTTAATATTGAGCATTGCGTAAAAAAAATATCACTGGATACATTGCCCGTAGTCTGCAAATCC-3′ (SEQ ID NO:13) (50 bp upstream of 1poA and forwardsacB-cat cassette primer; the 50 bp upstream of 1poA allows homologousrecombination to replace the gene), ANG1895′-CAGCCAGCGACGCGCTTGTGCTTCCCACGCATCGCCGGTCTGTTTGGTGGCCATGACCCGGGAATTACG-3′ (SEQ ID NO:14) (50 bp downstream of 1poA(reverse-complement) and rev sacB-cat cassette primer), ANG0655′-CGCAAACAACCGGGCATTAATC-3′ (SEQ ID NO:15) (forward upstream 1poAprimer, anneals 256 bp upstream of 1poA), ANG0665′-TTTGCTGCGGGTCACACTG-3′ (SEQ ID NO:16) (reverse downstream 1poAprimer, anneals 209 bp downstream of 1poA), AG35′-gctgcttggcgcgGCagaaaaacagcag-3′ (SEQ ID NO:17) (forward 1poA(K168A)mutagenesis primer; upper-case letters represent changes for 1poA(K168A)point mutation), AG4 5′-ctgctgtttttctGCcgcgccaagcagc-3′(SEQ ID NO:18)(reverse 1poA(K168A) mutagenesis primer).

Encapsulation of Bacteria in Monodisperse Droplets

Before mixing bacteria together with the other components of thereaction, the bacterial suspension was washed 3 times by centrifugationat 3000 rpm (Eppendorf) followed by resuspension of the pellet indistilled water. The bacteria was mixed together with primers, Taqmanprobe and PCR mix (2×ddPCR MasterMix, Biorad). The primers and Taqmanprobe were used at a working concentration of 1 μM and 250 nMrespectively. This mix was loaded into a 1 ml syringe back-filled withHFE-7500 oil, which was connected to a coaxial flow-focus device. Theoil used for the carrier phase was the droplet generation oil for probes(Biorad). The oil flow rate was set at 400 μlhr⁻¹ while the aqueous flowrate was set at 200 μlhr⁻¹. The emulsion was collected into PCR tubesand thermal-cycled on a T100 thermocycler (Bio-Rad), with the followingconditions: 10 min at 95° C., 35 cycles of 10 seconds at 95° C., 15seconds at 72° C. and 30 seconds at 55° C. To verify that the PCRreactions were specific, both bacterial samples were electrophoresed ona 2% agarose gel. No non-specific product was observed after imaging.

Primer and Probe Sequences for Taqman PCR, LpoA Amplification andSequencing

The primers for the detection of TolA were: TolA Forward5′-GTTGATTCAGGTGCGGTAGTT-3′ (SEQ ID NO:19), TolA Reverse5′-GCCTGCTGTTCCTTCATCTT-3′ (SEQ ID NO:20). The TolA probe sequence was5′-/6-FAM/ATCAAACCT/ZEN/GAAGGTGGCGATCCC/3IABkFQ/-3′(SEQ ID NO:21). Theprimers for LpoA amplification were: LpoA Forward5′-TTTACTGCGCGCGTTAATTG-3′(SEQ ID NO:22), LpoA Reverse5′-TTGCGGCTGAGGTTGTT-3′ (SEQ ID NO:23). The primer for TOPO Vectorsequencing was: M13 Forward (−20) 5′-GTAAAACGACGGCCAG-3′ (SEQ ID NO:24).

DEP Sorting

Thermalcycled drops were collected into a syringe filled with HFE-7500(3M) fluorinated oil, and left to cream for 10 minutes before startingthe syringe pump. The drops are then re-injected into the DEP device ata flow rate of 50 μlhr⁻¹, with the spacer oil flow rate set at 1000μlhr⁻¹. The flow rate for the 2nd oil spacer at the sorting junction wasset at 100 μlhr⁻¹. All the oil used for spacing droplets was HFE-7500.The moat was filled with 2M NaCl salt solution, as were the saltelectrodes. The PMTs were connected to a computer with LABVIEW softwareand a FPGA data acquisition card (National Instruments) for dropletfluorescence intensity recording and electrode activation. CustomLABVIEW software was written to enable dynamic adjustments of PMT gain,droplet fluorescence intensity thresholds for sorting, electrode ACvoltage pulse frequency and magnitude. The data acquisition rate forthis system was 200 kHz.

LpoA Sequencing Verification

Droplets from the positive DEP sort were collected into 1.5 ml Eppendorftubes. Chloroform (Sigma-Aldrich) and distilled water were pipetted overthe oil, with 20 μL of water used for every 200 μL of chloroform and 200μL of oil. The droplets were then vortexed for 10 minutes on a shaker,and then centrifuged at 14,000 rpm. The top layer of immiscible waterwas then extracted, of which 9 μL was used for PCR amplification. ThePCR amplification mixture included 1 μM forward and reverse LpoAsequencing primers, 1× Toptaq PCR master mix (Qiagen), and template fromthe broken drops in a total volume of 20 μL. The mixture was thenthermal-cycled with the following conditions: 10 minutes at 95° C., 35cycles of 10 seconds at 95° C., 15 seconds at 72° C. and 30 seconds at50° C. The PCR product was then cloned into a pCR4-TOPO vector (LifeTechnologies) using a TOPO TA cloning kit for sequencing (LifeTechnologies), following the manufacturer's instructions. This vectorwas transformed into electrocompetent E. coli TOP10 bacteria andstreaked onto LB plates with 50 μgml⁻¹ kanamycin for growth at 37° C.overnight. Colonies were picked at random for overnight growth in LBwith 50 μgml-1 kanamycin at 37° C., DNA extracted using a Qiagenminiprep kit, and then sent for Sanger sequencing (QuintaraBiosciences). The primer used for sequencing was the M13 Forward (−20)primer.

Results

Strategy of PACS

PACS provides single cell nucleic acid analysis and ultrahigh-throughputsorting of cells. PCR is a powerful technique for detecting microbesbecause it enables the use of temperatures near the boiling point ofwater to lyse cells and denature DNA; this allows PCR probes to annealto their complementary targets with higher efficiency and sequencespecificity than methods that rely on room-temperature hybridizationalone. Moreover, PCR results in exponential amplification of the targetDNA, yielding a bright signal that can be detected rapidly, as neededfor ultrahigh-throughput screening and FACS sorting. Additionally, byimplementing TaqMan PCR, it is possible to differentiate betweensequences with high specificity and to multiplex reactions tointerrogate several genomic regions within each microbe; this limitsfalse-positive identification and enables fine differentiation betweenspecies of similar type.

In these examples, microfluidic droplets are utilized. With microfluidicdevices, droplets can be generated and sorted at kilohertz rates andeach droplet utilizes just tens of picoliters of reagent, allowingmillions of PCR reactions to be performed with microliters of totalreagent. Moreover, because the aqueous droplets are suspended in aninert liquid oil, they can be flowed through microfluidic devices, whichallows multiple steps of processing, such as sampling fluid from, addingreagents to, and incubating and sorting the droplets; this allowsmultistep reactions to be performed in the droplets that are nototherwise possible.

Small genomic regions including hundreds of bases in length serve as“sequence biomarkers” to identify cells of interest. Based on the PCRsignal produced when a cell containing the sequence biomarker ispresent, droplet sorting is used to recover the entire genome of thecell.

Targeted Recovery of Microbial Genomes with PACS

PACS may be used to rapidly screen a large and diverse population ofmicrobes to identify and recover the genomes of those microbes thatcontain particular nucleic acids. This may be accomplished by performinga PCR reaction on each individual cell and then sorting the cells basedon the outcomes of the reactions.

FIG. 64 provides one example of a general workflow which may be utilizedfor the targeted recovery of microbial genomes with PACS. In someembodiments, first step in such experiments is to encapsulate themicrobes (FIG. 64, Panel a) in individual water-in-oil droplets usingmicrofluidic emulsification (FIG. 64, Panel b). PCR reagent may beincluded in the microbial suspension, but in certain embodiments, themicrobes and PCR reagent, which can include detergents to enhance lysis,may be combined on-chip via laminar co-flow followed by dropletgeneration. The microbes may be diluted so that there are on averageless than one per droplet, with the droplets loaded randomly inaccordance with a Poisson distribution. In some embodiments, thedroplets are ˜35 pL in volume, however in certain instances the volumevaried by greater than 5× up or down, and are collected into a PCR tubeand thermo-cycled (FIG. 64, Panel c). Thermocycling may be performed ona standard PCR system, although on-chip thermocyclers may also be usedfor an unbroken workflow in some instances. During PCR, the elevatedtemperature lyses the microbes and disrupts DNA-protein and DNA-DNAinteractions, providing the PCR primers with access to the cell's DNA.Droplets containing the genetic sequences being assayed for will resultin TaqMan PCR amplification, yielding a droplet that is bright withfluorescence at the emission wavelength of the TaqMan probe due to itsdegradation by the 5′ exonuclease activity of Taq polymerase. At thispoint in the process, a large quantity (e.g. millions) of droplets maybe present, some of which are fluorescent (e.g., contain a microbe withthe sequence targeted by the assay). Next, the droplets may be screenedusing ultrahigh-throughput dropometry and the positives may be recoveredwith dielectrophoretic (DEP) sorting (FIG. 64, Panel d). The sorteddroplets can be loaded into individual wells or pooled together andchemically ruptured to access their contents, providing genomic DNA ofthe target microbes.

Validation of PACS

To validate recovery of specific microbes with PACS, target cells werespiked into a background of non-target cells and the workflow depictedin FIG. 64 was implemented. Two different E. coli strains having twodifferences in their genome were employed: The first strain had thegenetic sequence for the membrane protein TolA knocked out (ATolA),whereas the second had TolA intact but was a double mutant on the LpoAgene, which is an outer membrane lipoprotein (LpoA K168A). The mixedpopulation was then run through PACS as described herein (FIG. 64,Panels a-f) sorting based on the presence of TolA, which should onlyrecover the LpoA double mutants. To characterize the efficiency of thePACS sorting, the genomic DNA of the sorted microbes was recovered andPCR-amplified and the portion of the LpoA gene containing the mutationswas sequenced (FIG. 64, Panel f). By comparing the number of sequencescontaining the double mutant and those without it, the efficiency withwhich PACS can discriminate between these cell types based on TolA wasestimated. This experiment demonstrated that cells may be differentiatedbased on the presence of a gene (TolA) at one location of the genome,and then correct sorting confirmed by analyzing a different gene (LpoA)far away on the same genome. The sequences analyzed post-sorting werefound not to be the product of the first PCR; they were present in thesorted mixture because they existed in the same genome that containedTolA and, thus, were sorted with it.

Efficiency of Single Cell Droplet PCR

To investigate the specificity of the TaqMan assay, control experimentswere performed in which clonal populations of the two cell types wereemulsified separately, and then analyzed using droplet single cellTaqMan PCR with primers and probes for the TolA gene, the results ofwhich are shown in FIG. 65, Panel a. For the droplets containing thedouble mutants (LpoA K168A), in which TolA is present, a “digital”fluorescence signal is observed, in which a small fraction of thedroplets are bright, and the remainder exhibit no fluorescence, asillustrated in FIG. 65, Panel a, upper; the fluorescent droplets containindividual K168A microbes, while the dim droplets are devoid of anycells and thus constitute what is expected when the target sequence(TolA) is not present within the droplet. To confirm this, the sameexperiment was performed with the knockout population (ΔTolA), theresults of which are shown in FIG. 65, Panel a, lower. Even though thestoichiometry of the ΔTolA cells is comparable to that of the K168Acells in the first experiment, such that similar loading rates wereexpected into the droplets, no fluorescent droplets were observed. Thisdemonstrates that the TaqMan assay is specific to cells that havesequences targeted by the selected primers. This is consistent withcontrol experiments performed in bulk on large numbers of the cells andalso with the properties of TaqMan PCR. To validate that the positivedroplets in the K168A experiment correspond to “digital” amplificationresulting from a TolA positive cell, the experiment was repeated fordifferent concentrations of K168A cells. For Poisson loading of thecells in droplets, the probability that a given droplet has x cells isgiven by:

$\begin{matrix}{{{P\left( {x;\lambda} \right)} = \frac{e^{- \lambda}\lambda^{x}}{x!}},} & (1)\end{matrix}$

where λ is the average number of cells per 35 pL droplet (FIG. 66).Bright drops correspond to x≥1, whereas x=0 relates to dark drops. Theproportion p of bright to dark drops depends on λ according to,

p=1−e ^(−λ)  (2)

This is a simple statement that as the concentration of cells insuspension increases, more of the droplets contain at least one cell. Torelate the number of cells in the droplets to the number of fluorescentdroplets observed at the conclusion of the assay, the fact that not alldroplets containing single cells undergo amplification should beaccounted for. That is, due to inefficiencies in the PCR, theprobability that the reaction undergoes amplification is less thanunity. We can account for this by rewriting the equation as

p=1−e ^(−5λ),  (3)

where k is the probability that a droplet containing a target cellyields a fluorescent signal. To measure, k, an important parameter thatdescribes the sensitivity with which positive cells are detected, theexperiment is repeated at different concentrations, (FIG. 65, Panel b).For k=1, the TaqMan reaction can be said to be perfectly efficient sothat every drop containing a cell yields a fluorescent signal. For k<1,the reaction is imperfect so that some droplets containing positivecells do not yield a fluorescent signal. Based on the current data, itis determined that 0.6<k<0.7, indicating that approximately 65% of thepositive cells are detected in the sample. This inefficiency may be aconsequence of the natural stochasticity of PCR, particularly inpicoliter volumes in which reagents may be limiting. Another explanationis that cell lysis is not perfectly efficient and in some of thedroplets the cells remain intact or the DNA targets inaccessible to theamplification primers, inhibiting the reaction. This effect can bemitigated by including PCR-compatible detergents in the droplets, whichaid cell lysis and solubilization of DNA targets and may improve singlecell PCR efficiency. Using more sophisticated multistep microfluidictechniques, it is also possible to include PCR incompatible lysisreagents, such as alkaline buffers, lysozyme, or proteases, to enablelysis of particularly durable microbes.

Recovery of Whole Bacterial Genomes with Droplet Sorting

At the conclusion of single cell droplet PCR, a collection of millionsof droplets may be present, some of which contain target microbes andare fluorescent. To recover the positive droplets and the genomes of thecells they contain, ultrahigh-throughput dielectrophoretic (DEP) dropletsorting may be used. An example of a suitable droplet sorterconfiguration is provided in FIG. 67. The droplet sorter includes adroplet reinjection inlet, a spacing inlet, and a sorting junction. Thedevice is surrounded by conducting aqueous “moats” that shield theinjected droplets from stray electric fields, which can unintentionallycoalesce droplets. These “moats” are designed so that they surround theoil channels, as illustrated in (FIG. 67).

Upon injection into the device, the thermocycled droplets are closepacked and spaced by oil in the spacing junction, as shown in FIG. 67,left. Spacing ensures that the droplets pass the detection region (FIG.67, middle) one at a time, so that the fluorescence of each droplet canbe measured individually. It also ensures that the droplets do not crowdthe sorting junction (FIG. 67, right), which can result in dropletcollisions that interfere with controlled sorting. After spacing, thedroplets pass through the detection region (FIG. 67, middle) and passthrough a focused laser beam; the laser excites the fluorescent dyes inthe droplets, causing them to emit light in proportion to the amount ofcleaved TaqMan probes they contain. Droplets that underwent successfulTaqMan amplification emit bright fluorescent light, while those that didnot appear dim. The fluorescent light is captured by the objective of amicroscope, filtered through dichroic minors and bandpass filters, andfocused onto the sensor of a photomultiplier tube (PMT). The PMT outputsa voltage proportional to the intensity of the fluorescent light. Theoil surrounding each droplet is not fluorescent; hence, when a dropletpasses through the detection laser, the PMT records a peak as a functionof time, as shown in FIG. 68, Panel a; each peak in the time tracecorresponds to a distinct droplet. The amplitude of a given peak isproportional to the intensity of the droplet, allowing bright TaqManpositive droplets to be differentiated from dim TaqMan negativedroplets, as illustrated by the bright droplet at t=32.5 ms.

To recover the bright droplets, a threshold voltage of 0.12 was set;this value varies between runs depending on the focusing optics and PMTgains and cleanly distinguishes between positive and negative droplets,as shown in FIG. 68, Panel a. Above this value, the computer isinstructed to sort the droplet, which it does by outputting analternating current (AC) pulse that is amplified to 1500 V and appliedto a conducting aqueous electrode in the sorting junction, asillustrated in FIG. 67, middle. Energizing the electrode generates anelectric field that polarizes the droplet in the sorting junction; thisproduces a dielectrophoretic attraction that pulls the droplet towardsthe electrode, deflecting it into streamlines that carry it into thecollection channel. When the electrode is not energized, the geometry ofthe sorting junction is designed so that the droplet follows streamlinesthat carry it into the waste channel. By selectively energizing theelectrodes based on the measured fluorescence of the droplets, TaqManpositive droplets were recovered and the negative droplets discarded, asshown in the images in FIG. 68, Panel b.

Sequence Verification of Sorted Genomes

Epifluorescence microscopy images (FIG. 68, Panel b) demonstrate thatthe dielectrophoretic sorter accurately sorts the bright from the dimdrops. To validate that PACS enables accurate single cell sorting basedon nucleic acid sequences, genomic DNA was recovered from the positivelysorted droplets for Sanger sequencing. The sorted droplets werechemically ruptured with the addition of chloroform and application ofmechanical shear, and the microbial genomes dispersed into aqueousbuffer. The K168A cell line has a double amino acid mutation of “AAA”encoding lysine to “GCA” encoding alanine, as seen in FIG. 69, Panel a.Since errors in the PCR preparation or the Sanger sequencing are rare,the above provides a high confidence read out with which to validate thePACS sorting. Two mixed ratios of the ATolA and TolA bacteria weretested, one where the mutant was present at 20% in the total population,and the other at 1%. For the 20% spike-in, 5 of 10 sequences before PACSwere positive for the mutant, whereas 9 of 10 were positive after PACS,as shown in FIG. 69, Panel b. The high pre-PACS frequency of the mutantmay be the result of random sampling variation, since only ten moleculeswere sequenced. Similarly, the 1% spike-in yielded no pre-PACS positivesin the ten molecule sample, while the post-PACS library was 9 of 10.Thus, for both spike-in ratios, a reasonable number of mutants pre-PACSand mostly mutants post-PACS were observed.

The preceding merely illustrates the principles of the invention. Itwill be appreciated that those skilled in the art will be able to devisevarious arrangements which, although not explicitly described or shownherein, embody the principles of the invention and are included withinits spirit and scope. Furthermore, all examples and conditional languagerecited herein are principally intended to aid the reader inunderstanding the principles of the invention being without limitationto such specifically recited examples and conditions. Moreover, allstatements herein reciting principles, aspects, and embodiments of theinvention as well as specific examples thereof, are intended toencompass both structural and functional equivalents thereof.Additionally, it is intended that such equivalents include bothcurrently known equivalents and equivalents developed in the future,i.e., any elements developed that perform the same function, regardlessof structure. The scope of the present invention, therefore, is notintended to be limited to the exemplary embodiments shown and describedherein. Rather, the scope and spirit of present invention is embodied bythe appended claims.

1-36. (canceled)
 37. A method comprising: obtaining a heterogeneoussample comprising nucleic acids; encapsulating, in a plurality ofmicrodroplets, one or more of the nucleic acids, nucleic acid synthesisreagents, and at least one detection component, the plurality ofmicrodroplets comprising an aqueous phase fluid in an immiscible phasecarrier fluid; incubating the plurality of microdroplets underconditions that promote nucleic acid synthesis reagent activity; sortingthe plurality of microdroplets based on identifying the at least onedetection component, to produce sorted microdroplets; and analyzing atleast one unamplified nucleic acid in at least one sorted microdropletof the sorted microdroplets.
 38. The method of claim 37, furthercomprising lysing a cell to release the nucleic acids prior toencapsulating the nucleic acid synthesis reagent and detection componentto the plurality of microdroplets.
 39. The method of claim 37, whereinanalyzing comprises analyzing epigenetic marks.
 40. The method of claim37, wherein identifying the at least one detection component indicatespresence of a sequence biomarker.
 41. The method of claim 37, whereinthe at least one detection component is a fluorescent detectioncomponent.
 42. The method of claim 41, wherein the fluorescent detectioncomponent hybridizes with a mutation of interest in nucleic acidsencapsulated in the plurality of microdroplets.
 43. The method of claim41, wherein the fluorescent detection component is a fluorescent beadcomprising a nucleotide sequence capable of hybridizing with a capturesequence associated with a mutation of interest in nucleic acidsencapsulated in the plurality of microdroplets.
 44. The method of claim37, wherein sorting comprises sorting the plurality of microdroplets viaflow cytometry.
 45. The method of claim 37, further comprising poolingtarget nucleic acids from the sorted microdroplets to provide anenriched pool of target nucleic acids.
 46. A method comprising:encapsulating, in at least one microdroplet of a plurality ofmicrodroplets, a nucleic acid and a nucleic acid synthesis reagent, theplurality of microdroplets comprising an aqueous phase fluid in animmiscible phase carrier fluid; introducing a detection component intothe at least one microdroplet; incubating the plurality of microdropletsunder conditions that promote nucleic acid synthesis reagent activityusing the at least one nucleic acid and the at least one nucleic acidsynthesis reagent; sorting the plurality of microdroplets comprising theat least one microdroplet based on identifying the at least onedetection component; and analyzing at least one unamplified nucleic acidfrom the at least one sorted microdroplet of the sorted plurality ofmicrodroplets.
 47. The method of claim 46, further comprising lysing acell to release the nucleic acid prior to encapsulating the nucleic acidsynthesis reagent into the at least one microdroplet.
 48. The method ofclaim 46, wherein analyzing comprises analyzing epigenetic marks. 49.The method of claim 46, wherein identifying the at least one detectioncomponent indicates presence of a sequence biomarker.
 50. The method ofclaim 46, wherein the at least one detection component is a fluorescentdetection component.
 51. The method of claim 50, wherein the fluorescentdetection component hybridizes with a mutation of interest in nucleicacids encapsulated in the plurality of microdroplets.
 52. The method ofclaim 50, wherein the fluorescent detection component is a fluorescentbead comprising a nucleotide sequence capable of hybridizing with acapture sequence associated with a mutation of interest in nucleic acidsencapsulated in the plurality of microdroplets.
 53. The method of claim46, wherein sorting comprises sorting the plurality of microdroplets viaflow cytometry.
 54. The method of claim 46, further comprising poolingtarget nucleic acids from the sorted microdroplets to provide anenriched pool of target nucleic acids.
 55. The method of claim 54,wherein analyzing at least one unamplified nucleic acid comprisessequencing one or more target nucleic acids.
 56. A method of enrichingnucleic acids, the method comprising: encapsulating, in at least onemicrodroplet of a plurality of microdroplets, at least one nucleic acidand at least one nucleic acid synthesis reagent, the plurality ofmicrodroplets comprising an aqueous phase fluid in an immiscible phasecarrier fluid; introducing a detection component into the at least onemicrodroplet; incubating the plurality of microdroplets under conditionsthat promote nucleic acid synthesis reagent activity; positioning theplurality of microdroplets in an aqueous phase carrier fluid to providea plurality of aqueous phase-in-immiscible phase-in aqueous phasemicrodroplets; and sorting the plurality of aqueous phase-in-immisciblephase-in aqueous phase microdroplets based on identifying the at leastone detection component, wherein identification of the detectioncomponent indicates the presence of nucleic acid amplification products;and analyzing at least one unamplified nucleic acid in at least onesorted microdroplet of the sorted microdroplets.